Tri-electrode apparatus and methods for molecular analysis

ABSTRACT

The claimed invention is an apparatus and method for performing impedance spectroscopy with a handheld measuring device. Conformal analyte sensor circuits comprising a porous nanotextured substrate and a conductive material situated on the top surface of the solid substrate in a circuit design may be used alone or in combination with a handheld potentiometer. Also disclosed are methods of detecting and/or quantifying target analytes in a sample using a handheld measuring device.

CROSS REFERENCE TO RELATED APPLICATION

This application claims priority to U.S. Provisional Patent ApplicationSer. Nos. 61/949,858 filed Mar. 7, 2014 and 62/110,141 filed Jan. 30,2015, the contents of each of which are incorporated herein byreference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates generally to the field of detectiondevices. More particularly, it concerns apparatus and methods utilizingthree electrode potentiostats to detect biomolecules and other targetanalytes in a concurrent manner.

2. Description of Related Art

The ability to design, cheap and disposable diagnostics and analyticalplatforms that are also biodegradable is of great value to health careas well as the environment. It has been established that size basedconfinement of biomolecules is critical for achieving enhancedsensitivity in diagnostics. Typically, size based confinement isachieved through complex fabrication processes as used for complementarymetal-oxide-semiconductor (CMOS) technologies, which increases the costper unit and increases the effective cost of the technology. Low costtechnologies use printed circuit boards which are difficult to disposeand add costs to the environment due to poor biodegradability.Paper-based microfluidics have been developed that typically use screenprinting technologies; however, issues remain with respect to achievingcontrolled fluid flow on top the surfaces.

Similarly, currently available market potentiostats are designed withthe focus of applicability to a wide range of electrical/electrochemicaltechniques. This leads to bulky form factors and expensive componentsused in their construction. Moreover, they are designed to be used forelectrochemical applications. Specific problems with such marketpotentiostats include the fact that they have large device form factors,making it difficult for use in point-of-care settings, have high noiseat low current and low voltage settings, have expensive and repetitivesoftware and firmware costs, have analog serial input/output interfaces,and have low robustness and non-universality in global application. Onthe other extreme, handheld portable potentiostats are very limited incustomizability and applicability to a range of applications. Portablepotentiostats are not noise efficient for biological applications andhence lack robustness. Specific problems with handheld potentiostatsinclude high noise at low current and low voltage settings, lowrobustness for application to biosensing, and minimal operation choicesfor electrochemical applications.

Currently available market potentiostats are available as two electrodeand three electrode systems. Both the currently available two electrodeand three electrode potentiostats apply a single input voltage betweentwo electrodes. This single applied input voltage suffers from limitedspecificity in detecting target analytes.

Therefore, there remains a need for affordable, efficient, biodegradablediagnostic platforms having enhanced specificity in detecting targetanalytes.

SUMMARY OF THE INVENTION

Exemplary embodiments of the claimed invention include apparatus andmethods for performing impedance spectroscopy with a handheldpotentiometer.

Exemplary embodiments include a method of detecting or quantifyingmultiple target analytes in a sample using a handheld measuring deviceand a conformal analyte sensor circuit comprising the steps of: (a)placing a sample containing multiple target analytes on a conformalsubstrate having a sensor circuit comprising a first electrode, a secondelectrode, and a third electrode; (b) applying a first alternating inputelectric voltage between the first electrode and the second electrode ata first phase angle; (c) applying a second alternating input electricvoltage between the third electrode and the second electrode at a secondphase angle, wherein the first phase angle and the second phase angleare separated by a constant delta phase angle; (d) measuring the outputcurrent at different frequencies and varying phase angles for differentanalytes; (e) amplifying an output current flowing from the firstelectrode and from the third electrode through the second electrodeusing a programmable gain amplifier; (f) sectioning an electrical doublelayer into a plurality of planes, wherein the electrical double layer isproximal to a surface of first electrode, a surface of the secondelectrode, and a surface of the third electrode; (g) varying the firstphase angle of the first input electric voltage and the second phaseangle of the second input electric voltage; (h) identifying the firstphase angle and the second phase angle at which a maximum impedancechange occurs; (i) measuring the impedance identified at the first phaseangle and the second phase angle; and (j) using the measured impedanceand associated phase angle at different frequencies to detect multipletarget analytes or calculate concentrations of target analytes by use ofa standard calibration curve.

Particular embodiments include an analyte sensor circuit comprising: asubstrate having a surface comprising a conductive material (with orwithout textured porosity) situated on the surface in a circuit design,thereby creating a circuit comprising a first electrode, a secondelectrode and a third electrode; a programmable gain amplifier operablycoupled to the first electrode, the second electrode, and the thirdelectrode; and a programmable microcontroller operably coupled to theprogrammable gain amplifier, the first electrode, the second electrode,and the third electrode, wherein the programmable microcontroller isconfigured to: (a) apply a first alternating input electric voltagebetween the first electrode and the second electrode of the conformalanalyte sensor circuit; (b) apply a second alternating input electricvoltage between the third electrode and the second electrode at a secondphase angle, wherein the first phase angle and the second phase angleare separated by a constant delta phase angle; (c) amplify an outputcurrent flowing from the first electrode and from the third electrodethrough the second electrode using a programmable gain amplifier; (d)section an electrical double layer into a plurality of planes in threedimensional space, wherein the electrical double layer is proximal to asurface of the first electrode, a surface of the second electrode and toa surface of the third electrode; (e) vary the first phase angle of thefirst input electric voltage and the second phase angle of the secondinput electric voltage; (f) identify the first phase angle and thesecond phase angle at which a maximum impedance change occurs; (g)measure the impedance identified at the first phase angle and the secondphase angle; and (i) use the measured impedance to detect the targetanalyte or calculate a concentration of the target analyte by use of astandard calibration curve.

In certain embodiments, the device comprises additional circuits andeach circuit comprises a first electrode, a second electrode and a thirdelectrode each operably coupled to the programmable gain amplifier. Inparticular embodiments, the programmable microcontroller is configuredto perform steps (a)-(i) for each of the additional circuits.

Exemplary embodiments include a device configured to detect and quantifyanalytes, the device comprising: a conformal sensor circuit; and ahandheld reader coupled to the conformal sensor circuit, wherein thedevice is configured simultaneously detect and quantify multiple targetanalytes from a single sample.

In certain embodiments, the conformal sensor circuit comprises: asubstrate having a surface comprising a conductive material situated onthe surface in a circuit design, thereby creating a circuit comprising afirst electrode, a second electrode and a third electrode; aprogrammable gain amplifier operably coupled to the first electrode, thesecond electrode, and the third electrode; and a programmablemicrocontroller operably coupled to the programmable gain amplifier, thefirst electrode, the second electrode, and the third electrode, whereinthe programmable microcontroller is configured to: (a) apply a firstalternating input electric voltage between the first electrode and thesecond electrode of the conformal analyte sensor circuit; (b) apply asecond alternating input electric voltage between the third electrodeand the second electrode at a second phase angle, wherein the firstphase angle and the second phase angle are separated by a constant deltaphase angle; (c) amplify an output current flowing from the firstelectrode and from the third electrode through the second electrodeusing a programmable gain amplifier; (d) section an electrical doublelayer into a plurality of planes in three dimensional space, wherein theelectrical double layer is proximal to a surface of the first electrode,a surface of the second electrode and to a surface of the thirdelectrode; (e) vary the first phase angle of the first input electricvoltage and the second phase angle of the second input electric voltage;(f) identify the first phase angle and the second phase angle at which amaximum impedance change occurs; (g) measure the impedance identified atthe first phase angle and the second phase angle; and (i) use themeasured impedance to detect the target analyte or calculate aconcentration of the target analyte by use of a standard calibrationcurve.

Exemplary embodiments include a method of detecting or quantifying atarget analyte in a sample using a handheld measuring device and aconformal analyte sensor circuit comprising the steps of: (a) placing asample containing multiple target analytes on a conformal substratehaving a sensor circuit comprising a first electrode, a secondelectrode, a third electrode, a fourth electrode, a fifth electrode anda sixth electrode; (b) applying a first alternating input electricvoltage between the first electrode and the second electrode at a firstphase angle; (c) applying a second alternating input electric voltagebetween the third electrode and the second electrode at a second phaseangle, wherein the first phase angle and the second phase angle areseparated by a first constant delta phase angle; (d) measuring a firstoutput current at different frequencies over a first range offrequencies and varying phase angles over a first range of phase angles;(e) amplifying the first output current flowing from the first electrodeand from the third electrode through the second electrode using aprogrammable gain amplifier; (f) sectioning a first electrical doublelayer into a plurality of planes in three dimensional space, wherein thefirst electrical double layer is proximal to a surface of firstelectrode, a surface of the second electrode, and a surface of the thirdelectrode; (g) varying the first phase angle of the first input electricvoltage and the second phase angle of the second input electric voltageover the first range of phase angles; (h) identifying the first phaseangle and the second phase angle at which a first maximum impedancechange occurs; (i) measuring the impedance identified at the first phaseangle and the second phase angle; (j) using the measured impedance atdifferent frequencies to detect a first target analyte or calculate aconcentration of the first target analyte by use of a standardcalibration curve; (k) applying a third alternating input electricvoltage between the fourth electrode and the fifth electrode at a thirdphase angle; (l) applying a fourth alternating input electric voltagebetween the sixth electrode and the fifth electrode at a fourth phaseangle, wherein the third phase angle and the fourth phase angle areseparated by a second constant delta phase angle; (m) measuring a secondoutput current at different frequencies over a second range offrequencies and varying phase angles over a second range of phaseangles; (n) amplifying the second output current flowing from the fourthelectrode and from the sixth electrode through the fifth electrode usingthe programmable gain amplifier; (o) sectioning a second electricaldouble layer into a plurality of planes, wherein the second electricaldouble layer is proximal to a surface of fourth electrode, a surface ofthe fifth electrode, and a surface of the sixth electrode; (p) varyingthe third phase angle of the third input electric voltage and the fourthphase angle of the fourth input electric voltage over the second rangeof phase angles; (q) identifying the third phase angle and the fourthphase angle at which a second maximum impedance change occurs; (r)measuring the impedance identified at the third phase angle and thefourth phase angle; and (s) using the measured impedance and phasechange at different frequencies to detect a second target analyte orcalculate a concentration of the second target analyte by use of astandard calibration curve. In particular embodiments, steps (a)-(j) areperformed concurrently with steps (k)-(s).

In certain embodiments, the first range of frequencies and the secondrange of frequencies are different. In particular embodiments, the firstrange of phase angles and the second range of phase angles aredifferent. In some embodiments, the first range of frequencies and thesecond range of frequencies are equal. In specific embodiments, thefirst range of phase angles and the second range of phase angles areequal.

Exemplary embodiments include a method of detecting or quantifying atarget analyte in a sample using a handheld measuring device and aconformal analyte sensor circuit comprising the steps of: (a) applying afirst input electric voltage between a first electrode and a secondelectrode of a conformal analyte sensor circuit; (b) applying a secondinput electric voltage between a third electrode and the secondelectrode of the conformal analyte sensor circuit; (c) amplifying anoutput current flowing from the first electrode and from the thirdelectrode through the second electrode using a programmable gainamplifier; (d) calculating an impedance by comparing the first inputelectric voltage and the second input electric voltage to the outputcurrent using a programmable microcontroller; and (e) detecting a targetanalyte or calculating a target analyte concentration from thecalculated impedance using a programmable microcontroller.

Exemplary embodiments include a method of detecting or quantifyingmultiple target analytes in a sample using a handheld measuring deviceand a conformal analyte sensor circuit comprising the steps of: (a)applying a first input electric voltage between a first electrode and asecond electrode of a conformal analyte sensor circuit; (b) applying asecond input electric voltage between a third electrode and the secondelectrode of the conformal analyte sensor circuit; (c) shifting anangular orientation of an electric field of the second input electricvoltage; (d) amplifying an output current flowing through the firstelectrode using a programmable gain amplifier; (e) detecting a presenceof one or more target analytes by comparing the angular orientation ofthe electric field to the output current. The types of analytes that canbe measured include analytes in liquid or gaseous analytes incorporatedinto liquid.

In exemplary embodiments, the first input electric voltage and thesecond input electric voltage have a frequency between 50 Hz and 5,000Hz. In certain embodiments, the first input electric voltage and thesecond input electric voltage are sinusoidal, and/or sawtooth wavesand/or square waves. In particular embodiments, the first input electricvoltage and the second input electric voltage are between 100 mV and 500mV, or more particularly between 50 mV and 200 mV, or still moreparticularly between 5 mV and 20 mV.

In specific embodiments, the output current is between 10 pA and 10 mA,or more particularly between 10 pA and 100 nA, or more particularlybetween 100 nA and 10 mA. In certain embodiments, the output current isamplified by a factor between 1 and 200. Particular embodiments furthercomprise calculating impedance as a function of frequency by applying afast Fourier transform and/or calculating impedance as a function offrequency using a Laplace transform. Certain embodiments furthercomprise calculating impedance as a function of frequency usingmulti-slice splitting and signal analysis. In particular embodiments,the angular orientation is shifted between 0 and 360 degrees. Specificembodiments further comprise displaying the calculated target analyteconcentration. Certain embodiments further comprise displaying thecalculated impedance. Particular embodiments further comprise displayingan output on an LCD display. Specific embodiments further comprisedisplaying an output on a smartphone. Certain embodiments furthercomprise providing an input using a mini-joystick. Particularembodiments further comprise providing an input using a smartphone. Inspecific embodiments, the measured impedance is non-faradaic.

In certain embodiments, the conformal analyte sensor circuit comprises:a solid substrate having a top surface, wherein the substrate comprisesa porous nanotextured substrate; and a conductive material situated onthe top surface of the solid substrate in a circuit design, therebycreating a circuit comprising the first electrode, the second electrode,and the third electrode. In particular embodiments, the porousnanotextured substrate has a porosity of 10×107 to 10×1018 pores/mm2, ormore particularly a porosity of 10×1010 to 10×1013 pores/mm2. Inspecific embodiments, the porous nanotextured substrate is an insulatingsubstrate. In certain embodiments, the porous nanotextured substrate ispaper or nitrocellulose. In particular embodiments, the conductivematerial is conductive ink or semi-conductive ink. In specificembodiments, the semi-conductive ink comprises carbon ink and additives,and in certain embodiments, the conductive ink is carbon, silver, ormetal or metal oxide nanoparticle-infused carbon inks.

In particular embodiments, the metal or metal-oxide nanoparticle-infusedcarbon ink is 1% by volume infused with gold, platinum, tantalum,silver, copper, tin, indium-tin oxide, grapheme, grapheme oxide, zincoxide, titanium oxide, iron oxide, or molybdenum oxide. In specificembodiments, the circuit is a nonlinear circuit, and in certainembodiments, the circuit is a non-ohmic circuit. Certain embodimentscomprise a base electrode surface, and in particular embodiments, thebase electrode surface is further coupled to a source circuit. Inspecific embodiments, the source circuit comprises a potentiostat,and/or a voltage source, and/or a current source.

In certain embodiments, the circuit does not contain a capture ligand orlabel-molecule. In particular embodiments, the conformal analyte sensorfurther comprises a redox material.

In exemplary embodiments, the analyte sensor circuit is assembled by amethod comprising: (a) providing the solid porous nanotexturedsubstrate; and (b) transferring the analyte sensor circuit design ontothe top surface of the porous nanotextured substrate using conductivematerial. In certain embodiments, transferring the circuit designcomprises dip coating. In particular embodiments, the feature resolutionof the circuit is up to 100 nanometers/0.1 micron. In specificembodiments, transferring the circuit design comprises embossing. Incertain embodiments, the feature resolution of the circuit is up to 100nanometers/0.1 micron. In particular embodiments, transferring thecircuit design comprises designing the circuit on a 3D printer andembossing the circuit onto the substrate. In specific embodiments, thefeature resolution of the circuit is up to 100 nanometers/0.1 micron. Incertain embodiments, the circuit design comprises masking andlithography. In particular embodiments, the feature resolution of thecircuit is 1-10 microns.

Exemplary embodiments include a handheld device for measuring a targetanalyte comprising: (a) a programmable gain amplifier configured to beoperably coupled to a first electrode, a second electrode, and a thirdelectrode; (b) a programmable microcontroller operably coupled to theprogrammable gain amplifier, the first electrode, the second electrode,and the third electrode; where the programmable microcontroller isoperable to apply a first alternating input electric voltage between thefirst electrode and the second electrode; the programmablemicrocontroller is operable to apply a second alternating input electricvoltage between the third electrode and the second electrode; theprogrammable gain amplifier is operable to amplify an alternating outputcurrent flowing from the first electrode and from the third electrodethrough the second electrode; the programmable microcontroller isoperable to calculate an impedance by comparing the first input electricvoltage and the second input electric voltage to the measured outputcurrent; and the programmable microcontroller is operable to calculate atarget analyte concentration from the calculated impedance.

Exemplary embodiments include a handheld device for measuring a targetanalyte comprising: (a) a programmable gain amplifier configured to beoperably coupled to a first electrode, a second electrode, and a thirdelectrode; (b) a programmable microcontroller operably coupled to theprogrammable gain amplifier, the first electrode, the second electrode,and the third electrode; where the programmable microcontroller isoperable to apply a first alternating input electric voltage between thefirst electrode and the second electrode; the programmablemicrocontroller is operable to apply a second alternating input electricvoltage between the third electrode and the second electrode; theprogrammable gain amplifier is operable to shift the angular orientationof an electric field of the second alternating input electric voltage;the programmable gain amplifier is operable to amplify an alternatingoutput current flowing through the third electrode; the programmablemicrocontroller is operable to calculate an amplitude of the alternatingoutput current; and the programmable microcontroller is operable todetect a presence of one or more target analytes by comparing theangular orientation to the amplitude of the alternating output current.

In certain embodiments of the handheld measuring device, theprogrammable microcontroller is operable to apply the first alternatinginput electric voltage and the second alternating input electric voltagethat have a frequency between 50 Hz and 1,000 Hz. In particularembodiments, the programmable microcontroller is operable to apply thefirst alternating input electric voltage and the second alternatinginput electric voltage that are sinusoidal. In specific embodiments, theprogrammable microcontroller is operable to apply the first alternatinginput electric voltage and the second alternating input electric voltagethat are sawtooth waves. In certain embodiments, the programmablemicrocontroller is operable to apply the first alternating inputelectric voltage and the second alternating input electric voltage thatare square waves. In particular embodiments, the programmable gainamplifier has a variable gain of between 1 and 200. In specificembodiments, the microcontroller is operable to apply a firstalternating input electric voltage and a second alternating inputelectric voltage of between 5 mV and 500 mV. In certain embodiments, thehandheld measuring device is operable to detect an output current of 10pA or greater. In particular embodiments, the programmablemicrocontroller comprises an analog to digital converter and a digitalto analog converter. In specific embodiments, the programmablemicrocontroller is operable to apply a fast Fourier transform to theinput electric voltage and output current to calculate impedance as afunction of frequency. In certain embodiments, the programmablemicrocontroller is operable to apply a Laplace transform to the inputelectric voltage and output current to calculate impedance as a functionof frequency. In particular embodiments, the programmablemicrocontroller is operable to use multi-slice splitting and signalanalysis to determine a frequency at which the impedance change is at amaximum or minimum. In specific embodiments, the programmablemicrocontroller is operable to shift the angular orientation from 0 to360 degrees.

Certain embodiments further comprise a liquid crystal display operablycoupled to the programmable microcontroller; a mini joystick operablycoupled to the programmable microcontroller; where the mini joystick isoperable to allow users to provide input; and the liquid crystal displayis capable of displaying output data. Particular embodiments furthercomprise a smartphone operably coupled to the programmablemicrocontroller; where the smartphone is operable to allow users toprovide input; and the smartphone is capable of displaying output data.In specific embodiments, the output data comprises the target analyteconcentration. In certain embodiments, the output data comprises theimpedance. In specific embodiments, the handheld measuring device doesnot contain a redox probe.

Exemplary embodiments include a method of calibrating a handheldmeasuring device by testing a plurality of solutions having known targetanalyte concentrations comprising: (a) applying a first input electricvoltage between a first electrode and a second electrode for each of theplurality of solutions; (b) applying a second input electric voltagebetween a third electrode and a second electrode for each of theplurality of solutions; (c) amplifying an output current flowing fromthe first electrode and from the third electrode through the secondelectrode using a programmable gain amplifier; (d) calculating animpedance for each of the plurality of solutions by comparing the firstinput electric voltage and the second input electric voltage to theoutput current using a programmable microcontroller; (e) calculatingcoefficients of the equation zi=b1x2+b2x+c, wherein zi is the impedance,x is the known target analyte concentrations, and b1, b2, and c are thecoefficients.

Exemplary embodiments include a kit comprising a conformal circuit and ahandheld measuring device as described herein.

In some embodiments, the handheld potentiometer comprises an LCD screen,mini-joystick, a first electrode port, a second electrode port, a thirdelectrode port, programmable microcontroller, and programmable gainamplifier. In other embodiments, the handheld potentiometer comprises asmartphone, cable, potentiostat adaptor, first electrode port, secondelectrode port, third electrode port, programmable microcontroller, andprogrammable gain amplifier. In some embodiments, the handheldpotentiometer comprises a programmable microprocessor instead of aprogrammable microcontroller.

In some embodiments, the handheld device for measuring a target analytecomprises (a) a programmable gain amplifier configured to be operablycoupled to a first electrode, a second electrode, and a third electrode(b) a programmable microcontroller operably coupled to the programmablegain amplifier, the first electrode, the second electrode, and the thirdelectrode wherein the programmable microcontroller is operable to applyan alternating input electric voltage between the first electrode andthe second electrode and an alternating input electric voltage betweenthe third electrode and the second electrode; the programmable gainamplifier is operable to amplify an alternating output current flowingfrom the first electrode through the second electrode and amplify analternating output current flowing from the third electrode through thesecond electrode; the programmable microcontroller is operable tocalculate an impedance by comparing the input electric voltages to themeasured output currents; and the programmable microcontroller isoperable to calculate a target analyte concentration from the calculatedimpedance.

In some embodiments, the handheld device for measuring a target analytecomprises (a) a programmable gain amplifier configured to be operablycoupled to a first electrode, a second electrode, and a third electrode(b) a programmable microcontroller operably coupled to the programmablegain amplifier, the first electrode, the second electrode, and the thirdelectrode wherein the programmable microcontroller is operable to applyan alternating input electric voltage between the first electrode andthe second electrode and an alternating input electric voltage betweenthe third electrode and the second electrode; the programmablemicrocontroller is operable to vary an orientation of the electric fieldbetween the third and the reference electrode; the programmable gainamplifier is operable to determine the current response at the thirdelectrode; and the programmable microcontroller is operable to determinethe presence of a plurality of target analytes based upon the currentresponse compared to the angle of orientation.

In some embodiments, the third-second electrode electric field has thesame orientation as the first-reference electrode electric field. Insome embodiments, the third-second electrode electric field isperpendicular to the orientation of the first-second electrode electricfield. In some embodiments, the orientation of the third-secondelectrode electric field is varied from 0 to 360 degrees in relation tothe first-second electrode electric field. In some embodiments, thethird electrode is parallel to the first and second electrodes. In otherembodiments, the third electrode is perpendicular to the first andsecond electrodes. In some embodiments, the programmable microcontrolleris operable to apply an input electric voltage between the firstelectrode and the second electrode and between the third electrode andthe second electrode that has a frequency between 50 Hz and 1,000 Hz. Insome embodiments, the programmable microcontroller is operable to applyan input electric voltage that is sinusoidal. In some embodiments, theprogrammable microcontroller is operable to apply an input electricvoltage that is a sawtooth wave. In some embodiments, the programmablemicrocontroller is operable to apply an input electric voltage that is asquare wave. In some embodiments, the programmable gain amplifier has avariable gain of between 1 and 200. In some embodiments, themicrocontroller is operable to apply an input electric voltage ofbetween 10 mV and 2 V. In some embodiments, the handheld measuringdevice is operable to detect an output current 10 pA or greater. In someembodiments, the programmable microcontroller comprises an analog todigital converter and a digital to analog converter. In someembodiments, the programmable microcontroller is capable of measuring adifference in phase between the input electric voltages and the outputcurrents. In some embodiments, the programmable microcontroller isoperable to apply a fast Fourier transform to the input electricvoltages and output currents to calculate impedance as a function offrequency. In some embodiments, the programmable microcontroller isoperable to apply a Laplace transform to the input electric voltages andoutput currents to calculate impedance as a function of frequency. Insome embodiments, the programmable microcontroller is operable to usemulti-slice splitting and signal analysis to determine a frequency atwhich the impedance change is at a maximum or minimum. In someembodiments, the device further comprises a liquid crystal displayoperably coupled to the programmable microcontroller; a mini joystickoperably coupled to the programmable microcontroller; wherein the minijoystick is operable to allow users to provide input; and the liquidcrystal display is capable of displaying output data. In someembodiments, the device further comprises a smartphone operably coupledto the programmable microcontroller; wherein the smartphone is operableto allow users to provide input; and the smartphone is capable ofdisplaying output data. In some embodiments, the output data comprisesthe target analyte concentration(s). In some embodiments, the handheldmeasuring device does not contain a redox probe.

The conformal analyte sensor circuit comprises a porous nanotexturedsubstrate and a conductive material situated on the top surface of thesolid substrate in a circuit design, thereby creating a circuitcomprising a first electrode, a second electrode, and a third electrode.The porosity of the nanotextured substrate is determined by the targetanalyte to be measured. In some embodiments, the porous nanotexturedsubstrate has a porosity at or between 10×10⁷ and 10×10¹⁸ pores/mm². Insome embodiments, the porous nanotextured substrate has a porosity at orbetween 10×10¹⁰ and 10×10¹³ pores/mm². In some embodiments, the porousnanotextured substrate is an insulating substrate. In some embodiments,the porous nanotextured substrate is paper or nitrocellulose.

The conductive material may be any appropriate material known to thoseof skill in the art. In some embodiments, the conductive material isconductive ink or semi-conductive ink. In some embodiments, thesemi-conductive ink comprises carbon ink and additives. In someembodiments, the conductive ink is carbon, silver, or metal or metaloxide nanoparticle-infused carbon inks. In some embodiments, the metalor metal-oxide nanoparticle-infused carbon ink is 1% by volume infusedwith gold, platinum, tantalum, silver, copper, tin, indium-tin oxide,grapheme, grapheme oxide, zinc oxide, titanium oxide, iron oxide, ormolybdenum oxide.

The circuit may be a nonlinear circuit or a non-ohmic circuit. In someembodiments, the circuit is further defined as a base electrode surface.In some embodiments, the base electrode surface is further connected toa source current. In some embodiments, the source current is apotentiostat. In some embodiments, the source circuit is a voltagesource. In some embodiments, the source circuit is a current source. Insome embodiments, the circuit does not contain a capture ligand orlabel-molecule. In some embodiments, the conformal analyte sensorfurther comprises a redox material.

In some embodiments, any of the conformal analyst sensor circuitsdisclosed herein is assembled by a method comprising (a) providing thesolid porous nanotextured substrate; and (b) transferring the analytesensor circuit design onto the top surface of the porous nanotexturedsubstrate using conductive material. In some embodiments, transferringthe circuit design comprises dip coating. In such embodiments, thefeature resolution of the circuit is up to 100 nanometers/0.1 micron. Insome embodiments, transferring the circuit design comprises embossing.In such embodiments, the feature resolution of the circuit is up to 100nanometers/0.1 micron. In some embodiments, transferring the circuitdesign comprises designing the circuit on a 3D printer and embossing thecircuit onto the substrate. In such embodiments, the feature resolutionof the circuit is up to 100 nanometers/0.1 micron. In some embodiments,transferring the circuit design comprises masking and lithography. Insuch embodiments, the feature resolution of the circuit is 1-10 microns.

In some embodiments, disclosed is a kit comprising any of the conformalanalyst sensor circuits disclosed herein and any of the handheldmeasuring devices disclosed herein.

The handheld potentiostats and porous nanotextured conformal circuitsdisclosed herein may be used separately or in combination to detectand/or quantify a target analyte. In some embodiments, disclosed is amethod of detecting a target analyte comprising spotting a sample on adisclosed conformal analyte sensor circuit, wherein the sample wicksthrough the porous nanotextured substrate and the circuit design,attaching the conformal analyte sensor circuit to a source circuit, anddetecting the target analyte in the sample with a source circuit. Insome embodiments, the source circuit is a potentiostat. In someembodiments, the source circuit is a voltage source. In someembodiments, the source circuit is a current source. In someembodiments, the sample contains 1-10 μl of a fluid. In someembodiments, the target analyte is a protein, DNA, RNA, SNP, smallmolecules, pathogens heavy metal ions, or physiological ions. In someembodiments, the sample is not labeled. In some embodiments, detectingthe target analyte comprises detecting an electrical change.

In some embodiments, disclosed is a method of detecting or quantifying atarget analyte in a sample using a handheld measuring device comprisingthe steps of (a) applying input electric voltages between a firstelectrode and a second electrode and between a third electrode and thesecond electrode, (b) amplifying output currents flowing from the firstelectrode through the second electrode and flowing from the thirdelectrode through the second electrode using a programmable gainamplifier, (c) calculating an impedance by comparing the input electricvoltages to the output currents using a programmable microcontroller,and (d) calculating a target analyte concentration from the calculatedimpedance using a programmable microcontroller.

In some embodiments, disclosed is a method of detecting or quantifying atarget analyte in a sample using a handheld measuring device comprisingthe steps of (a) applying input electric voltages between a firstelectrode and a second electrode and between a third electrode and thesecond electrode, (b) amplifying output currents flowing from the firstelectrode through the second electrode and flowing from the thirdelectrode through the second electrode using a programmable gainamplifier, (c) shifting an orientation of an electric field between thethird electrode and the second electrode, (d) measuring a currentresponse at the third electrode using a programmable microcontroller,and (d) determining an identity of a target analyte by comparing thecurrent response to the orientation using a programmablemicrocontroller.

In some embodiments, the third electrode is parallel to the firstelectrode and the second electrode. In some embodiments, the thirdelectrode is perpendicular to the first electrode and the secondelectrode. In some embodiments, the electric field of the third-secondelectrodes is oriented ninety degrees from the electric field of thefirst-second electrodes. In some embodiments, the third-referenceelectrode electric field has the same orientation as the first-secondelectrode electric field. In some embodiments, the orientation of thethird-second electrode electric field is varied from 0 to 360 degrees inrelation to the first-second electrode electric field. In someembodiments, the input electric voltages have a frequency between 50 Hzand 1,000 Hz. In some embodiments, the input electric voltages aresinusoidal. In some embodiments, the input electric voltages aresawtooth waves. In some embodiments, the input electric voltages aresquare waves. In some embodiments, the input electric voltages arebetween 100 mV and 500 mV. In some embodiments, the input electricvoltages are between 50 mV and 200 mV. In some embodiments, the inputelectric voltages are between 5 mV and 20 mV. In some embodiments, theoutput currents are between 10 pA and 10 mA. In some embodiments, theoutput currents are between 10 pA and 100 nA. In some embodiments, theoutput currents are between 100 nA and 10 mA. In some embodiments, theoutput currents are amplified by a factor between 1 and 200. In someembodiments, the method further comprises calculating impedance as afunction of frequency by applying a fast Fourier transform and or aLaplace transform. In some embodiments, the method further comprisescalculating impedance as a function of frequency using multi-slicesplitting and signal analysis. In some embodiments, the method furthercomprises displaying the calculated target analyte concentration. Insome embodiments, the method further comprises displaying an output onan LCD display. In some embodiments, the method further comprisesdisplaying an output on a smartphone. In some embodiments, the methodfurther comprises providing an input using a mini-joystick. In someembodiments, the method further comprises providing an input using asmartphone. In some embodiments, the measured impedance is non-faradaic.

In some embodiments, disclosed is a method of detecting or quantifying atarget analyte in a sample using a handheld measuring device comprisingthe steps of (a) applying input electric voltages between a firstelectrode and a second electrode and between an third electrode and thesecond electrode, (b) amplifying output currents flowing from the firstelectrode through the second electrode and flowing from the thirdelectrode through the second electrode using a programmable gainamplifier, (c) calculating a difference in a phase of the output currentto the phase of first input electric voltage and the phase of the secondinput electric voltage using a programmable microcontroller, and (d)detecting a presence of one or more target analytes by determiningmaximum differences in the phase of the output current using aprogrammable microcontroller. In some embodiments, the input electricvoltages have a frequency between 50 Hz and 1,000 Hz. In someembodiments, the input electric voltages are sinusoidal. In someembodiments, the input electric voltages are sawtooth waves. In someembodiments, the input electric voltages are square waves. In someembodiments, the input electric voltages are between 100 mV and 500 mV.In some embodiments, the input electric voltages are between 50 mV and200 mV. In some embodiments, the input electric voltages are between 5mV and 20 mV. In some embodiments, the output currents are between 10 pAand 10 mA. In some embodiments, the output currents are between 10 pAand 100 nA. In some embodiments, the output currents are between 100 nAand 10 mA. In some embodiments, the output currents are amplified by afactor between 1 and 200. In some embodiments, the method furthercomprises displaying the calculated target analyte concentration. Insome embodiments, the method further comprises displaying an output onan LCD display. In some embodiments, the method further comprisesdisplaying an output on a smartphone. In some embodiments, the methodfurther comprises providing an input using a mini-joystick. In someembodiments, the method further comprises providing an input using asmartphone.

The handheld potentiometer detects concentrations of a target analyte byapplying alternating voltages between the first and second electrodesand between the third and second electrodes. The alternating voltageapplied between the first and second electrodes differs in phase fromthe voltage applied between the third and second electrodes by 90degrees. The applied alternating voltages result in a current flowingfrom the first electrode through the second electrode and a currentflowing from the third electrode through the second electrode. Theresulting currents are amplified by a programmable amplifier and passedonto the programmable microcontroller. The programmable microcontrollercompares the applied voltages to the resulting currents to calculate theimpedance of the tested sample. The impedance is used to calculate theconcentration of the target analyte in the tested sample. In someembodiments, to perform testing of a target analyte using the handheldpotentiometer, the handheld potentiometer is first calibrated by testingand calculating the impedance of samples containing known quantities ofthe target analyte. In some embodiments, the system applies voltages ofvarying frequencies and determines the frequency at which the maximumimpedance change occurs for a particular tested analyte.

The claimed system may perform non-Faradaic electrochemical impedancespectroscopy (EIS) by testing samples without using a redox electrode.

In some embodiments, disclosed herein is a method of calibrating ahandheld measuring device by testing a plurality of solutions havingknown target analyte concentrations comprising (a) applying inputelectric voltages between a first electrode and a second electrode andbetween a third electrode and a second electrode for each of theplurality of solutions, (b) calculating an impedance for each of theplurality of solutions by comparing the input electric voltages to theoutput currents using a programmable microcontroller, and (c)calculating coefficients of the equation z₁=b₁x²+b₂x+c, wherein z_(i) isthe impedance, x is the known target analyte concentrations, and b₁, b₂,and c are the coefficients.

Exemplary embodiments may be used in conjunction with samples asprovided below.

A. Samples

Samples can come from a wide variety of sources. In one aspect, thesample is derived from a living organism, including a plant, animal(veterinary uses) or human. Such samples may involve solid material suchas feces or tissues (including biopsies), tissue extracts, or fluids,including body fluids such as saliva, sputum, tears, blood, serum,plasma, urine, exudate, transudate, spinal fluid, semen or nasaldischarge. Such samples may be solubilized or diluted, as needed, toperform the assays of the present invention. Solvents for use insolubilizing or diluting samples include water, acetone, methanol,toluene, ethanol or others.

Other samples, are manufactured, industrial or environmental, and may ormay not contain living cells or organisms. Such sample may include soil,water, foodstuffs, alcoholic beverages, building products, bulkchemicals or reagents, including drugs. Again, such samples may besolubilized or diluted, as needed, to perform the assays of the presentinvention.

B. Targets

Autoimmune Antigens or Antibodies Thereto. Autoimmune diseases can begenerally classified as antibody-mediated, T-cell mediated, or acombination of antibody-mediated and T-cell mediated. Thus, antibodiesor T-cell receptors can be identified with specificity to a variety ofendogenous antigens. Such auto-antibodies (e.g., anti-nuclearantibodies) may be implicated in various disease includinginsulin-dependent (type I) diabetes mellitus, rheumatoid arthritis,multiple sclerosis, systemic lupus erythematosus (SLE), and inflammatorybowel disease (i.e., Crohn's disease and ulcerative colitis). Otherautoimmune diseases include, without limitation, alopecia areata,acquired hemophilia, ankylosing spondylitis, antiphospholipid syndrome,autoimmune hepatitis, autoimmune hemolytic anemia, cardiomyopathy,celiac sprue dermatitis, chronic fatigue immune dysfunction syndrome(CFIDS), chronic inflammatory demyelinating polyneuropathy,Churg-Strauss syndrome, cicatricial pemphigoid, CREST syndrome, coldagglutinin disease, discoid lupus, essential mixed cryoglobulinemia,fibromyalgia, fibromyositis, Guillain-Barr syndrome, idiopathicpulmonary fibrosis, idiopathic thrombocytopenic purpura, IgAnephropathy, juvenile arthritis, lichen planus, myasthenia gravis,polyarteritis nodosa, polychondritis, polyglandular syndromes,dermatomyositis, primary agammaglobulinemia, primary biliary cirrhosis,psoriasis, Raynaud's phenomena, Reiter's syndrome, sarcoidosis,stiff-man syndrome, Takayasu arthritis, temporal arteritis/giant cellarteritis, uveitis, vasculitis, and vitiligo.

In particular autoimmune diseases, antibodies to self antigens arefrequently observed. For example for systemic lupus erythematosusautoantibodies have been described to single-stranded anddouble-stranded DNA or RNA (Vallin et al., 1999; Hoet et al., 1999; yenVenrooij, 1990). The levels of autoantibodies found in the serum ofautoimmune patients very often are found to correlate with diseaseseverity. The pattern of autoantibodies that arise, e.g., in human SLE,suggest that intact macromolecular particles, such as RNA- orDNA-containing complexes, could themselves be immunogenic andanti-nucleic acid antibodies could therefore arise (Lotz et al., 1992;Mohan et al., 1993). Such DNA or RNA released from, e.g., apoptoticcells or DNA- or RNA-containing microbes present in serum of autoimmunepatients, could be responsible for inflammation that contributes to theautoimmune disease (Fatenejad, 1994; Malmegrim et al., 2002; Newkirk etal., 2001). Indeed CpG-containing sequences could be identified from SLEserum that induces an efficient immune response dominated by IFN-α.secretion that is thought to contribute the development of to autoimmunediseases (Magnusson et al., 2001; Ronnblom et al., 2001). In addition,the epitopes for anti-RNA antibodies could be identified and arecomposed of G,U-rich sequences (Tsai et al., 1992; Tsai et al., 1993).G,U-rich sequences appear to be natural ligands for TLR7 and TLR8 and,therefore, can mediate immune stimulatory responses that in principlecould contribute to autoimmune diseases or the development of autoimmunediseases (PCT/US03/10406).Specific antigens to which auto-antibodies are produced includeβ2-glycoprotein, cardiolipin, CCP, CENP, GBM, gliadin, Jo-1, LKM1, La,MPO, Parietal Cell antigens, PR3, Ro, SS-B/La, SS-A/Ro, Scl-70, Sm,sperm transglutaminase, TPO and U1RNP.Infectious Agents.Infections refer to any condition in which there is an abnormalcollection or population of viable intracellular or extracellularmicrobes in a subject. Various types of microbes can cause infection,including microbes that are bacteria, microbes that are viruses,microbes that are fungi, and microbes that are parasites. Detection ofantigens or nucleic acids associated with these microbes, or antibodiesthereto, is contemplated in accordance with the present invention.

Bacteria include, the 83 or more distinct serotypes of pneumococci,streptococci such as S. pyogenes, S. agalactiae, S. equi, S. canis, S.bovis, S. equinus, S. anginosus, S. sanguis, S. salivarius, S. mitis, S.mutans, other viridans streptococci, peptostreptococci, other relatedspecies of streptococci, enterococci such as Enterococcus faecalis,Enterococcus faecium, staphylococci, such as Staphylococcus epidermidis,Staphylococcus aureus, Hemophilus influenzae, pseudomonas species suchas Pseudomonas aeruginosa, Pseudomonas pseudomallei, Pseudomonas mallei,brucellas such as Brucella melitensis, Brucella suis, Brucella abortus,Bordetella pertussis, Borellia species, such as Borellia burgedorferiNeisseria meningitidis, Neisseria gonorrhoeae, Moraxella catarrhalis,Corynebacterium diphtheriae, Corynebacterium ulcerans, Corynebacteriumpseudotuberculosis, Corynebacterium pseudodiphtheriticum,Corynebacterium urealyticum, Corynebacterium hemolyticum,Corynebacterium equi, etc. Listeria monocytogenes, Nocordia asteroides,Bacteroides species, Actinomycetes species, Treponema pallidum,Leptospirosa species, Haemophilus species, Helicobacter species,including Helicobacter pylori, Treponema species and related organisms.The invention may also be useful against gram negative bacteria such asKlebsiella pneumoniae, Escherichia coli, Proteus, Serratia species,Acinetobacter, Yersinia pestis, Francisella tularensis, Enterobacterspecies, Bacteroides and Legionella species, Shigella species,Mycobacterium species (e.g., Mycobacterium tuberculosis, Mycobacteriumbovis or other mycobacteria infections), Mycobacterium avium complex(MAC), Mycobacterium marinum, Mycobacterium fortuitum, Mycobacteriumkansaii, Yersinia infections (e.g., Yersinia pestis, Yersiniaenterocolitica or Yersinia pseudotuberculosis) and the like.

In addition, the invention contemplates detection of parasitic organismssuch as Cryptosporidium, Entamoeba, Plasmodium spp., such as Plasmodiumfalciparum, Plasmodium malariae, Plasmodium ovale, and Plasmodium vivaxand Toxoplasma gondii, Giardia, Leishmania, Trypanasoma, Trichomonas,Naegleria, Isospora belli, Trichomonas vaginalis, Wunchereria, Ascaris,Schistosoma species, Cyclospora species, for example, and for Chlamydiatrachomatis and other Chlamydia infections such as Chlamydia psittaci,or Chlamydia pneumoniae, for example. Of course it is understood thatthe invention may be used on any pathogen against which an effectiveantibody can be made.

Fungal and other mycotic pathogens (some of which are described in HumanMycoses (1979; Opportunistic Mycoses of Man and Other Animals (1989);and Scrip's Antifungal Report (1992), are also contemplated as a targetof diagnosis. Fungi disease contemplated in the context of the inventioninclude, but are not limited to, Aspergillosis, Black piedra,Candidiasis, Chromomycosis, Cryptococcosis, Onychomycosis, or Otitisexterna (otomycosis), Phaeohyphomycosis, Phycomycosis, Pityriasisversicolor, ringworm, Tinea barbae, Tinea capitis, Tinea corporis, Tineacruris, Tinea favosa, Tinea imbricata, Tinea manuum, Tinea nigra(palmaris), Tinea pedis, Tinea unguium, Torulopsosis, Trichomycosisaxillaris, White piedra, and their synonyms, to severe systemic oropportunistic infections, such as, but not limited to, Actinomycosis,Aspergillosis, Candidiasis, Chromomycosis, Coccidioidomycosis,Cryptococcosis, Entomophthoramycosis, Geotrichosis, Histoplasmosis,Mucormycosis, Mycetoma, Nocardiosis, North American Blastomycosis,Paracoccidioidomycosis, Phaeohyphomycosis, Phycomycosis, pneumocysticpneumonia, Pythiosis, Sporotrichosis, and Torulopsosis, and theirsynonyms, some of which may be fatal. Known fungal and mycotic pathogensinclude, but are not limited to, Absidia spp., Actinomadura madurae,Actinomyces spp., Allescheria boydii, Alternaria spp., Anthopsisdeltoidea, Apophysomyces elegans, Arnium leoporinum, Aspergillus spp.,Aureobasidium pullulans, Basidiobolus ranarum, Bipolaris spp.,Blastomyces dermatitidis, Candida spp., Cephalosporium spp.,Chaetoconidium spp., Chaetomium spp., Cladosporium spp., Coccidioidesimmitis, Conidiobolus spp., Corynebacterium tenuis, Cryptococcus spp.,Cunninghamella bertholletiae, Curvularia spp., Dactylaria spp.,Epidermophyton spp., Epidermophyton floccosum, Exserophilum spp.,Exophiala spp., Fonsecaea spp., Fusarium spp., Geotrichum spp.,Helminthosporium spp., Histoplasma spp., Lecythophora spp., Madurellaspp., Malassezia furfur, Microsporum spp., Mucor spp., Mycocentrosporaacerina, Nocardia spp., Paracoccidioides brasiliensis, Penicillium spp.,Phaeosclera dematioides, Phaeoannellomyces spp., Phialemonium obovatum,Phialophora spp., Phoma spp., Piedraia hortai, Pneumocystis carinii,Pythium insidiosum, Rhinocladiella aquaspersa, Rhizomucor pusillus,Rhizopus spp., Saksenaea vasiformis, Sarcinomyces phaeomuriformis,Sporothrix schenckii, Syncephalastrum racemosum, Taeniolella boppii,Torulopsosis spp., Trichophyton spp., Trichosporon spp., Ulocladiumchartarum, Wangiella dermatitidis, Xylohypha spp., Zygomyetes spp. andtheir synonyms. Other fungi that have pathogenic potential include, butare not limited to, Thermomucor indicae-seudaticae, Radiomyces spp., andother species of known pathogenic genera.Examples of viruses that have been found in humans include but are notlimited to: Retroviridae (e.g., human immunodeficiency viruses, such asHIV-1 (also referred to as HTLV-III, LAV or HTLV-III/LAV, or HIV-III;and other isolates, such as HIV-LP; Picornaviridae (e.g., polio viruses,hepatitis A virus; enteroviruses, human Coxsackie viruses, rhinoviruses,echoviruses); Calciviridae (e.g., strains that cause gastroenteritis);Togaviridae (e.g., equine encephalitis viruses, rubella viruses);Flaviviridae (e.g., dengue viruses, encephalitis viruses, yellow feverviruses); Coronaviridae (e.g., coronaviruses); Rhabdoviridae (e.g.,vesicular stomatitis viruses, rabies viruses); Filoviridae (e.g., ebolaviruses); Paramyxoviridae (e.g., parainfluenza viruses, mumps virus,measles virus, respiratory syncytial virus); Orthomyxoviridae (e.g.,influenza viruses); Bunyaviridae (e.g., Hantaan viruses, bunga viruses,phleboviruses and Nairo viruses); Arenaviridae (hemorrhagic feverviruses); Reoviridae (e.g., reoviruses, orbiviurses and rotaviruses);Bornaviridae; Hepadnaviridae (Hepatitis B virus); Parvoviridae(parvoviruses); Papovaviridae (papilloma viruses, polyoma viruses);Adenoviridae (most adenoviruses); Herpesviridae (herpes simplex virus(HSV) 1 and 2, varicella zoster virus, cytomegalovirus (CMV), herpesvirus; Poxviridae (variola viruses, vaccinia viruses, pox viruses); andIridoviridae (e.g., African swine fever virus); unclassified viruses(e.g., the agent of delta hepatitis (thought to be a defective satelliteof hepatitis B virus), Hepatitis C; Norwalk and related viruses, andastroviruses); and resipiratory syncytial virus (RSV).Other medically relevant microorganisms have been described extensivelyin the literature, e.g., see Medical Microbiology (1983), the entirecontents of which is hereby incorporated by reference.Cancer Antigens.Many human cancers express cell surface molecule that are specific tothe cancer cell, i.e., they are not expressed or expressed in greatlyreduced quantity by normal human somatic cells. The role of theseantigens in cancerogenesis and cancer progression is often poorlyunderstood, however, independent of their biological functions theseantigens are attractive antibody targets for diagnostic applications.Such tumor markers include alpha-feto protein, beta-2-microglobulin,bladder tumor antigen, CA 15-3, CA 19-9, CA 72-4, CA-125, calcitonin,carcinoembryonic antigen, epidermal growth factor receptor, estrogenreceptor, human chorionic gonadotropin, Her-2/neu, neuron-specificenolase, NPM22, progesterone receptor, prostate specific antigen,prostate-specific membrane antigen, prostatic acid phosphatase, S-100,TA-90 and thyroglobulin.Toxins, Metals and Chemicals.A particular type of chemical or biological agent is a toxin. Toxins canbe biological, i.e., produced by an organism. These include toxins thatmay be used in biological warfare or terrorism, including ricin, anthraxtoxin, and botulism toxin. Other toxins are pesticides (insecticides,herbicides; e.g., organophosphates), industrial contaminants (heavymetals, such as cadmium, thallium, copper, zinc, selenium, antimony,nickel, chromium, arsenic, mercury or lead; complex hydrocarbons,include PCBs, and petroleum byproducts; asbestos), and chemical warfarereagents (sarin, soman, cyclosarin, VX, VG, GV, phosgene oxime, nitrogenmustard, sulfur mustard and cyanogen chloride). Table 1 below shows afurther list of toxic industrial chemicals (TICs). A specific list of 12banned persistent organic pollutants includes PCBs, DDT, dioxins,chlordane, furans, hexochlorobenzene, aldrin, mirex, dieldrin,toxaphene, endrin, and heptachlor.

TABLE 1 TICs listed by hazard index High Medium Low Ammonia (CAS#7664-41-7) Acetone cyanohydrin (CAS# 75-86-5) Allyl isothiocyanate (CAS#57-06-7) Arsine (CAS# 7784-42-1) Acrolein (CAS# 107-02-8) Arsenictrichloride (CAS# 7784-34-1) Boron trichloride (CAS# 10294-34-5)Acrylonitrile (CAS# 107-13-1) Bromine (CAS# 7726-95-6) Boron trifluoride(CAS# 7637-07-2) Allyl alcohol (CAS# 107-18-6) Bromine chloride (CAS#13863-41-7) Carbon disulfide (CAS# 75-15-0) Allylamine (CAS# 107-11-9)Bromine pentafluoride (CAS# 7789-30-2) Chlorine (CAS# 7782-50-5) Allylchlorocarbonate (CAS# 2937-50-0) Bromine trifluoride (CAS# 7787-71-5)Diborane (CAS# 19287-45-7) Boron tribromide (CAS# 10294-33-4) Carbonylfluoride (CAS# 353-50-4) Ethylene oxide (CAS# 75-21-8) Carbon monoxide(CAS# 630-08-0) Chlorine pentafluoride (CAS# 13637-63-3) Fluorine (CAS#7782-41-4) Carbonyl sulfide (CAS# 463-58-1) Chlorine trifluoride (CAS#7790-91-2) Formaldehyde (CAS# 50-00-0) Chloroacetone (CAS# 78-95-5)Chloroacetaldehyde (CAS# 107-20-0) Hydrogen bromide (CAS# 10035-10-6)Chloroacetonitrile (CAS# 7790-94-5) Chloroacetyl chloride (CAS# 79-04-9)Hydrogen chloride (CAS# 7647-01-0) Chlorosulfonic acid (CAS# 7790-94-5)Crotonaldehyde (CAS# 123-73-9) Hydrogen cyanide (CAS# 74-90-8) Diketene(CAS# 674-82-8) Cyanogen chloride (CAS# 506-77-4) Hydrogen fluoride(CAS# 7664-39-3) 1,2-Dimethylhydrazine (CAS# 540-73-8) Dimethyl sulfate(CAS# 77-78-1) Hydrogen sulfide (CAS# 7783-0604) Ethylene dibromide(CAS# 106-93-4) Diphenylmethane-4.4′-diisocyanate (CAS# 101-68-8) Nitricacid, fuming (CAS# 7697-37-2) Hydrogen selenide (CAS# 7783-07-5) Ethylchlroroformate (CAS# 541-41-3) Phosgene (CAS# 75-44-5) Methanesulfonylchloride (CAS# 124-63-0) Ethyl chlorothioformate (CAS# 2941-64-2)Phosphorus trichloride (CAS# 7719-12-2) Methyl bromide (CAS# 74-83-9)Ethyl phosphonothioic dichloride (CAS# 993-43-1) Sulfur dioxide (CAS#7446-09-5) Methyl chloroformate (CAS# 79-22-1) Ethyl phosphonicdichloride (CAS# 1066-50-8) Sulfuric acid (CAS# 7664-93-9) Methylchlorosilane (CAS# 993-00-0) Ethyleneimine (CAS# 151-56-4) Tungstenhexafluoride (CAS# 7783-82-6) Methyl hydrazine (CAS# 60-34-4)Hexachlorocyclopentadiene (CAS# 77-47-4) Methyl isocyanate (CAS#624-83-9) Hydrogen iodide (CAS# 10034-85-2) Methyl mercaptan (CAS#74-93-1) Iron pentacarbonyl (CAS# 13463-40-6) Nitrogen dioxide (CAS#10102-44-0) Isobutyl chloroformate (CAS# 543-27-1) Phosphine (CAS#7803-51-2) Isopropyl chloroformate (CAS# 108-23-6) Phosphorusoxychloride (CAS# 10025-87-3) Isopropyl isocyanate (CAS# 1795-48-8)Phosphorus pentafluoride (CAS# 7647-19-0) n-Butyl chloroformate (CAS#592-34-7) Selenium hexafluoride (CAS# 7783-79-1) n-Butyl isocyanate(CAS# 111-36-4) Silicon tetrafluoride (CAS# 7783-61-1) Nitric oxide(CAS# 10102-43-9) Stibine (CAS# 7803-52-3) n-Propyl chloroformate (CAS#109-61-5) Sulfur trioxide (CAS# 7446-11-9) Parathion (CAS#: 56-38-2)Sulfuryl fluoride (CAS# 2699-79-8) Perchloromethyl mercaptan (CAS#594-42-3) Tellurium hexafluoride (CAS# 7783-80-4) sec-Butylchloroformate (CAS# 17462-58-7) n-Octyl mercaptan (CAS# 111-88-6)tert-Butyl isocyanate (CAS# 1609-86-5) Titanium tetrachloride (CAS#7550-45-0) Tetraethyl lead (CAS# 78-00-2) Tricholoroacetyl chloride(CAS# 76-02-8) Tetraethyl pyroposphate (CAS# 107-49-3) Trifluoroacetylchloride (CAS# 354-32-5) Tetramethyl lead (CAS# 75-74-1) Toluene2.4-diisocyanate (CAS# 584-84-9) Toluene 2.6-diisocyanate (CAS# 91-08-7)Plant Products.In certain embodiments, the present invention will allow one to assessthe content of plant materials. For example, one can measure the healthof a plant by measuring the nutrient content of the plants' leaves. Onecan also make decisions about harvesting of crops by assessing thecontent of fruit or vegetable tissue. For example, in wine-making, thesugar content of grapes is an important factor in determining harvesttime. Also, when selecting crops for breeding, identifying plants withvarious desirable traits (nutrient content, expression of endogenousproducts or transgenes) is critical.Drugs.In another aspect of the invention, the assays maybe used to detect ormeasure drugs in samples. The drugs may be therapeutic agents, and theassay is designed to assess drug levels in the subject with the goal ofoptimizing dosage. Alternatively, illicit drugs may be detected, andinclude alcohol, amphetamines, methamphetamine, MDMA, barbiturates,phenobarbitol, benzodiazepines, cannabis, cocaine, codeine, morphine,cotinine, heroin, LSD, methadone, PCP, or licit drugs banned forparticular purposes, such as sporting events, including anabolicsteroids, hormones (EPO, hGH, IGF-1, hCG, insulin, corticotrophins) β2agonists, anti-estrogens, diuretics, stimulants, andglucocorticosteroids.Lipids.Lipids are biologically relevant targets for assays of the presentinvention. For example, the ability to detect and quantitate lipids inthe blood can serve to assess risk of atherosclerotic disease, as wellas to monitor the efficacy of therapy therefore. Thus, LDL, HDL andtriglyceride measurements are of use.Sugars.While assessing sugar levels may be of general medical interest, sugarsare particularly relevant to diabetes management and therapy. Othersugars of relevance include those produced by bacteria and fungi inbiofilm formation, and those produced during food or beverageproduction.Nucleic Acids.Nucleic acids are significant biological targets for determining thehealth status of subjects. Nucleic acids of interest include genes(genomic sequences), mRNA (transcripts), miRNAs, or fragments thereof.The nucleic acids may be endogenous to the subject, such as thosemolecules that may be elevated or decreased in disease states, norexogenous, such as those of a pathogen (virus, bacteria, parasite)present in the subject (discussed above).

As used herein the specification, “a” or “an” may mean one or more. Asused herein in the claim(s), when used in conjunction with the word“comprising”, the words “a” or “an” may mean one or more than one.

The use of the term “or” in the claims is used to mean “and/or” unlessexplicitly indicated to refer to alternatives only or the alternativesare mutually exclusive, although the disclosure supports a definitionthat refers to only alternatives and “and/or.” As used herein “another”may mean at least a second or more.

Throughout this application, the term “about” is used to indicate that avalue includes the inherent variation of error for the device, themethod being employed to determine the value, or the variation thatexists among the study subjects.

Other objects, features and advantages of the present invention willbecome apparent from the following detailed description. It should beunderstood, however, that the detailed description and the specificexamples, while indicating preferred embodiments of the invention, aregiven by way of illustration only, since various changes andmodifications within the spirit and scope of the invention will becomeapparent to those skilled in the art from this detailed description.

BRIEF DESCRIPTION OF THE DRAWINGS

The following drawings form part of the present specification and areincluded to further demonstrate certain aspects of the presentinvention. The invention may be better understood by reference to one ormore of these drawings in combination with the detailed description ofspecific embodiments presented herein.

FIG. 1 High resolution optical micrograph demonstrating the surfaceporosity and interaction between the pores and the electrode surfaces,including a scanning electron micrograph showing conformal featuregeneration between the electrode and the surrounding matrix with aschematic rendering of the interaction between the measurement entityand the surrounding matrix.

FIG. 2 A schematic representation of an electrode configuration with athird electrode parallel to a first electrode and a second electrode.

FIG. 3 A schematic representation of an electrode configuration with athird electrode perpendicular to a first electrode and a secondelectrode

FIG. 4 A schematic representation of an electrical double layer andelectrode surface.

FIG. 5 A schematic representation of electrodes configured as analytesensors on a substrate surface.

FIG. 6 A schematic representation of a representative three electrodehandheld potentiostat.

FIG. 7 Handheld potentiostat device.

FIG. 8 A smartphone embodiment of a handheld potentiostat.

FIG. 9 A Bode plot illustrating impedance vs. frequency for differentproteins.

FIG. 10 A Bode plot illustrating impedance vs. frequency for differentproteins.

FIG. 11 A plot illustrating the current response vs. rotational anglefor different proteins.

FIG. 12 A flowchart illustrating the operation of the potentiostat.

FIG. 13 A table listing various species of target analytes system andassociated system configurations.

FIG. 14 A graph of a change in impedance versus concentration oflipopolysaccharide.

FIG. 15 A graph of a change in impedance versus concentration ofprocalcitonin.

FIG. 16 A graph of a change in impedance versus concentration oflipoteichoic acid.

FIG. 17 A graph of measured impedance regarding the detection of miRNAsequence (P4) with a specific capture probe (P2) at various temperaturesand times.

FIG. 18 A graph of estimated impedance regarding interaction ofnon-specific miRNA sequence with capture probe (P2) at varioustemperatures and times.

FIG. 19 A graph of estimated impedance regarding the interaction ofsalmon sperm DNA with capture probe (P2) at various temperatures andtimes.

DESCRIPTION OF ILLUSTRATIVE EMBODIMENTS

The conformal circuits disclosed herein leverage the surface roughnessthat exists at the nanoscale on paper and other nanoporous substratesfor designing conformal electric circuits. Circuit parameters such ascurrent and impedance are modulated when the circuit elements aremodulated due to the detection of biomolecules through a single stepimmunoassay format. This technology can be applied towards detecting andquantifying a variety of target analytes, including but not limited toproteins, DNA, RNA, SNP, and a diverse range of biomolecules.

In some embodiments, disclosed herein are conformal circuits comprisinga solid substrate having a top surface, wherein the substrate comprisesporous nanotextured substrate and a conductive material situated on thetop surface of the solid substrate in a circuit design, thereby creatinga circuit. Also disclosed are methods of making the same, as well asmethods of detecting and/or quantifying a variety of target analytesusing the same. FIG. 1 depicts an example design of such a conformalcircuit.

These conformal circuits are developed using a combination of tracketching and conductive ink deposition to create nonlinear and non-ohmiccircuits. Three types of circuits are generated: (a) impedance-basedresistive capacitive (RC) coupled circuits, (b) diode-based circuits,and (c) transistor-based circuits. The RC circuits work on the principleof electrochemical impedance spectroscopy, and the diode and transistorcircuits are biased by an AC voltage source resulting in changes tocurrent characteristics as a function of detection of species ofinterest.

The conformal circuits disclosed herein may have an electrode that isconducting, semi-conducting, or semi-insulating. An increase inconductivity is suitable for achieving increased sensitivity in theimpedance measurement format. In the diode and transistor format,semi-conducting/semi-insulating materials are used to obtain adequatebarrier potential to obtain the appropriate threshold gating/gatecurrent characteristics. For diode performance, the material combinationis used to obtain barrier potentials mimicking silicon of up to 0.7 V.For transistor performance, barrier potentials between 0.2 and 0.7 aregenerated.

The conformal circuits disclosed herein generate electrical changes, asopposed to electrochemical changes. In particular, the conformalcircuits disclosed herein generate electrical/electrochemical changeswithout the use of a reduction-oxidation probe changes, as opposed toelectrochemical changes mediated through a redox electrode. The use of aredox probe for electrochemical detection produces irreversible changesto the biomolecule resulting in indirect and modified detection that isnot representative of the biomolecules. Thus, this capability isachieved by tailoring the deposition of the conductive material onto thenanoporous substrate. In addition, both passive and active sensing arespecifically contemplated.

The conformal circuit and detection devices disclosed herein can bedesigned to detect quantitatively (e.g., an EIS electronic reader). Inaddition, the system can be designed to detect a single analyte using asingle circuit or multiple analytes using separate circuits, which maybe the same or different, depending on the variety of analytes beingdetected and/or analyzed.

A. Detection Devices

A variety of electrical components can be attached to the electricallyconductive material pathways in order to detect and quantify the targetanalyte. Non-limiting examples of electronic components includeintegrated circuits, resistors, capacitors, transistors, diodes,mechanical switches, batteries, and external power sources, non-limitingexamples of batteries include button cell batteries, and non-limitingexamples of external power source include an AC voltage source. Theelectrical components can be attached using, e.g., known adhesives. Insome embodiments, the conformal circuits discussed in detail above canbe coupled to a source circuit for the purpose of detecting thebiomolecule. In particular embodiments, the conformal circuit can becoupled to potentiostats, voltage sources, current sources, oroperational amplifier circuits for doing a wide range of simple andcomplex mathematical operations, addition, subtraction, integration, anddifferentiation.

Impedance spectroscopy is a widely used three electrode electrochemicaltechnique for studying material binding efficiency on electrodes.Recently, innovative changes to classical electrochemical impedancespectroscopy have made it suitable for applications to biomedicalstudies. These modifications demand application of very low voltages anddetection at very small currents, both of which fall into the noisethreshold of existing devices. In addition, most currently availablemarket potentiostats require additional equipment, such as a computer,and detailed user input, making it difficult for point-of-careimplementation. Further, currently available market potentiostats applya single input voltage between electrodes, providing reduced specificityof detected target analytes.

Disclosed herein are customizable handheld potentiostats devices forperforming electrochemical impedance spectroscopy using a threeelectrode configuration at fixed and variable frequencies. The noveltechnique used in the disclosed device reduces noise effects andachieves sensitive detection, and the components used are programmableand highly customizable to the desired application. Consequently, thisachieves maximum performance efficiency from the device by programmingit to function best in the desired range of operation for the particulardesired task. In addition, the disclosed device applies two orthogonalinput voltages, improving the specificity of detected target analytes.

In the devices disclosed herein, impedance spectroscopy is used todetect and quantify binding activity on an electrode surface. Thebinding of biomolecules to an electrode surface causes a change incurrent flow, which can be used to identify and quantify the biomoleculebeing bound. The detection threshold for the device is approximately inthe femtomolar or femtogram/mL concentration ranges, but it can be inthe attogram/ml range for some biomolecules.

Exemplary embodiments disclosed herein comprise a first electrode 108, asecond electrode 106, and a third electrode 110. In certain embodiments,the first, second and third electrodes 108, 106 and 110 are planar. Inexemplary embodiments, first and second electrodes 108 and 106 aredisposed parallel to each other in an X-Y plane. In some embodiments,third electrode 110 is parallel to first and second electrodes 108 and106, as shown in FIG. 2. In other embodiments, third electrode 110 isdisposed perpendicular to first and second electrodes 108 and 106, asshown in FIG. 3. In exemplary embodiments, first, second and thirdelectrodes, 108, 106 and 110 may be deposited on a porous nanotexturedsubstrate as shown in FIG. 1 to form a conformal circuit.

During operation, AC voltages can be applied at terminals 158, 156 and160 for first, second, and third electrodes 108, 106 and 110respectively. The AC voltage may be a sinusoidal, sawtooth, or squarewave signal. The resulting currents flowing from the first electrodethrough the second electrode terminal and from the third electrodethrough the second electrode terminal can then be measured. Referringnow to FIG. 4, when a conductive solution is present at the electrodesurface and a voltage is applied to the electrodes, a capacitiveelectrical double layer 115 is formed in the solution near an electrodesurface 111, e.g., between the electrode surface and a diffuse layer119. As properties (e.g., the phase angle, frequency or amplitude) ofthe applied voltage or voltages change, the distance between electricaldouble layer 115 and electrode surface 111 also changes. The propertiesof the applied voltage(s) can be manipulated, and output responses(e.g., current) from electrical double layer 115 can be measured viaHelmholtz probing to determine properties of the conductive solution(e.g., the identification or concentration of an analyte in thesolution).

In particular embodiments, a first electric field can be applied tofirst and second electrodes 106 and 108, while a second electric fieldis applied to second and third electrodes 108 and 110. In particularembodiments, the region within electrical double layer 115 where themaximal change to the measured charge occurs (in a capacitance format)can be identified. This region can then be used to interpret the type ofmolecule being interrogated. Virtual slicing (with sub-nanometerresolution scanning step) of electrical double layer 115 can beaccomplished using a scanning modality by varying properties of theapplied voltage such that there is a correlation in the sub-nanometerresolution between the applied voltage and the height within electricaldouble layer 115.

In certain embodiments, the scanning mechanism is adaptive as itcompares the current measurement with the previously measured impedanceat the prior frequency or phase step. In particular embodiments, fromthis comparison an algorithm can be applied to interpret if there is avariation or change to the measured signal which is two standarddeviations from the previous measurement. In exemplary embodiments, thestep size can first change linearly if the variation to the measuredsignal is within the two standard deviation threshold; then scanning offrequency or phase can take place logarithmically to the next decadewhere the scanning can then resume linearly.

Referring now to FIG. 5, first, second and third electrodes 108, 106 and110 can be configured as multiple sensors 181, 182 and 183 on asubstrate surface 180. For purposes of clarity, not all sensors onsurface 180 are labeled, and individual electrodes are not labeled inthe sensors. It is understood that the electrode configurations for eachsensor may comprise one of the configurations provided in thisdisclosure. Bi-functional linkers 191, 192 and 193 (including forexample, a dithiobis succinimidyl propriante linker) can be coupled tosensors 181, 182 and 183 as shown in FIG. 5. A target-specific antibody171, 172 and 173 can be coupled to bi-functional linkers 191, 192 and193 configured to capture biomolecules 161, 162 and 163. In certainembodiments, each sensor may comprise a bi-functional linker andtarget-specific antibody configured to detect a different biomolecule sothat multiple unique biomolecules can be detected by a plurality ofsensors on surface 180.

During operation, a first electric field (represented by plane 113) isapplied at a first phase angle to first and second electrodes 108 and106 for one or more of sensors 181, 182 and 183. In addition, a secondelectric field (represented by plane 117) is applied at a second phaseangle to second and third electrodes 106 and 110. In exemplaryembodiments, the phase angle of electric fields 113 and 117 can bemodulated. With both electric fields 113 and 117 being applied to secondelectrode 106, the phase angle between the electric fields 113 and 117is constant (e.g., the fields are locked in phase and separated by aconstant delta phase angle). In the embodiment shown, electric field 113is applied parallel to substrate surface 180. In exemplary embodiments,parameters of electric field 113 (e.g., the frequency) can be modulatedto change the distance between surface 180 and electric field 113 todetect ionic interactions between a biomolecule 185 and surface 180.Accordingly, the applied electric fields can be modulated to probe theionic interactions in the Z-direction (perpendicular to surface 180) bychanging the frequency, as well as they X-Y directions (parallel tosurface 180) by changing the phase angle.

The modulus and imaginary components of the measured impedance ofelectric field 113 can be analyzed with the change in parameters.Distinctive markers of biomolecule 185 can be identified based on thechanges in modulus and imaginary components of the measured impedance.As explained further below for example, a known biomolecule can beapplied to surface 180 and the modulus and imaginary components measuredwith applied input parameter modulation to establish a standardcalibration curve with different calibration response profiles fordifferent biomolecules. In addition, the phase angle of applied electricfields 113 and 117 can be varied, and the rotational angle and phasecurrent response analyzed to determine distinctive markers ofbiomolecules. Again, a known biomolecule can be applied to surface 180and the rotational and phase current response measured with phase anglemodulation to establish a standard calibration curve with differentresponse profiles for different biomolecules.

The establishment of calibration response profiles can be prepared invarious manners. In one embodiment, a linker is deposited on thesubstrate, the substrate is saturated with a moiety specific for thetarget analyte, e.g., a target specific antibody, a blocking buffer isapplied to the receptor moiety saturated conformal circuit surface tominimize nonspecific binding or adsorption of other competing moleculesonto the sensor surface, a buffer wash is performed, and the targetanalyte, e.g., antigen, is dosed onto the circuit. In designing thecalibration curve for a target molecule, such as an antigen, increasingdoses of the antigen are applied onto the conformal circuit andimpedance measurements are obtained until steady state is reached. Anincreasing change to the measured impedance is expected with increasingdose of the target molecule such as an antigen. Once the calibrationcurve has been designed, an unknown dose of a test target molecule suchas an antigen can be tested onto the antibody/receptor moiety saturatedsensor surface, and the change in impedance is then evaluated againstthe calibration curve to determine the dose of the test target molecule.

In exemplary embodiments, the assignment to the native or unbiasedsurface is first performed where the buffer helps identify the effectiveimpedance of the system. This impedance can help determine the signalthreshold of the assay, and this number can change as a function of thebuffer and the contact impedance of the electrode. Impedance matchingbetween this measured baseline and the baseline of the potentiostat canbe performed, and the conformal electrode can help to elongateelectrical double layer 115 to enable the adaptive probing. The inherentsurface charge, height, isoelectric behavior, flexibility (e.g.,steric/conformational) of the capture probe can enable the assignment ofthe baseline measurement.

A diagram depicting an example of one configuration of handheldpotentiostat is found at FIG. 7. The handheld potentiostat 200 comprisesan LCD display 104. The LCD display 104 provides a user interface thatdisplays input and output data. For example, the LCD display may show aninput voltage, an input frequency, a wave type, a target analyte name, amolecular concentration, an impedance, and a phase angle. The handheldpotentiostat 200 may also comprise a mini joystick 124, which enablesthe user to provide input to the handheld potentiostat 200. For example,the mini joystick 124 may be used to navigate menus on the LCD display104 and increase or decrease input voltage and frequency values. In someembodiments, the handheld potentiostat 200 may comprise buttons or akeypad in addition to or instead of a mini joystick 124. The handheldpotentiostat further comprises a first electrode port 202, a secondelectrode port 204, and a third electrode port 206. The electrode ports202, 204, and 206 are used to connect wire leads to the first, second,and third electrodes.

A block diagram representing one possible potentiostat/electrodeconfiguration is found at FIG. 6. The heart of operation for thepotentiostat is carried out in the programmablemicrocontroller/microprocessor 100. The first operation of themicrocontroller is providing user interface support through an LCDdisplay 104. The serial peripheral interface SPI2 is used to communicateinformation processed in the microcontroller 100 to the LCD display 104.The microcontroller 100 uses VCC and DC Offset to supply power to theLCD display 104.

User input/response to options displayed on the LCD display 104 isreceived as analog signals through an analog-analog communicationbetween the mini joystick 124 and microcontroller 100. Using the minijoystick 124, the user may select the electrical signal parameters,e.g., voltage, frequency, wave type, to be applied to the firstelectrode 108, second electrode 106, and third electrode 110.Alternatively, the mini joystick 124 is used to select the type ofmolecule to be detected. After the test concludes, the LCD display 104may display the names of analytes detected, the numerical concentrationof the molecule(s) in the tested sample, impedances, and orientationangles.

Next, the microcontroller 100 is programmed to perform impedancespectroscopy characterization on the attached electrochemical sensor.Based upon the electrical signal parameters or molecule selected by theuser, the programmable microcontroller 100 generates an first AC voltageon lines DAC1+ and DAC− that is applied to the first electrode 108 andsecond electrode 106, respectively, and a second AC voltage on linesDAC2+ and DAC− that is applied to third electrode 110 and secondelectrode 106, respectively. The AC voltages may be amplified byamplifiers 112, 114, and 116. In some embodiments, the resultingvoltages of the first electrode 108 and third electrode 110 may fed backto the microcontroller 100 on the Signal line. The resulting voltage maydiffer from the applied voltage due to chemical reactions in the testedsolution. The microcontroller 100 digitizes the voltage value of thesecond electrode 106, and the digitized voltage is used by themicrocontroller 100 to adjust the applied AC voltage levels on linesDAC1+, DAC2+, and DAC−. In some embodiments, the voltages of the firstelectrode 108 and third electrode 110 may fed back to the programmablegain amplifier 102 on the Signal+ line. The programmable gain amplifiermay digitize the voltage value of the second electrode 106 and send thedigitized voltage to the microcontroller 100 over line SPI1, and thedigitized voltage is used by the microcontroller 100 to adjust the ACvoltage level on lines DAC+ and DAC−.

After two AC voltages are applied and a sample of an electricallyconductive solution contacts the sensor, an AC current flows from thefirst electrode 108 through the second electrode 106 and from thirdelectrode 110 through the second electrode 106. The amount of currentflowing through the second electrode 106 depends upon the voltagesapplied to the second electrode 106, first electrode 108, thirdelectrode 100, the binding of molecules on the electrodes, and thesolution used. A programmable gain amplifier 102 measures the currentflowing through the second electrode 106. Specifically, thetransconductance amplifier 118 feeds a current to the programmable gainamplifier on line 1A. The current may be filtered by a bandpass filter122. The bandpass filter 122 is automatically adjusted to permit signalsat the applied frequency while rejecting noise at other frequencies. Theprogrammable gain amplifier 102 then generates an amplified voltage fromthe current that is fed into the programmable microcontroller on lineADC. The amplification is necessary as the microcontroller operationthresholds are much greater than the small voltages and currentsgenerated in this impedance spectroscopy application. In someembodiments, the amplified voltage on line ADC ranges between 20 mV and6 V. If the amplified voltage on line ADC is too high or too low, themicrocontroller 100 sends a signal to the programmable gain amplifier102 over line SPI1 to increase or decrease the gain. In someembodiments, the binary gain of the programmable gain amplifier 102 maybe adjusted between 1 and 128. In some embodiments, the scope gain ofthe programmable gain amplifier 102 may be adjusted between 1 and 200.The Signal+ line provides a reference voltage to the programmable gainamplifier 102 to calculate gain. The Signal+ voltage may be amplified byamplifier 120 and filtered by a bandpass filter 122.

The microcontroller 100 converts the analog amplified voltage to adigital signal. The microcontroller 100 then compares the digitizedamplified voltage, which represents the amount of current flowing fromthe first electrode 108 and third electrode 110 through the secondelectrode 106, to the voltages applied to the first electrode 108 andsecond electrode 106 and to third electrode 110 and second electrode 106to determine the impedance of the solution being tested. Themicrocontroller 100 performs arithmetic operations to calculate phaseand amplitude changes in the amplified voltage with respect to theapplied voltage as a function of frequency. Impedance is calculatedusing the following formula:

$Z = \frac{V_{m}\sin\;\omega\; t}{I_{m}{\sin\left( {{\omega\; t} + \varphi} \right)}}$where V_(m) represents the amplitude of the applied voltage, I_(m)represents the amplitude of the resulting current flowing between theelectrodes, ω is the angular frequency of the applied voltage andresulting current, and φ is the difference in phase between the appliedvoltage and resulting current. Phase changes are calculated using thefollowing formula:

$\Phi = \frac{\Delta\;{\varphi(v)}}{\Delta\;{\varphi(i)}}$which is the ratio of the phase components of the input voltage to thephase components of the output current. In some embodiments, themicrocontroller 100 uses a fast Fourier transform to determine the phaseand amplitude changes as a function of frequency. In some embodiments,the microcontroller 100 uses a Laplace transform to determine the phaseand amplitude changes as a function of frequency. In some embodiments,the microcontroller 100 performs multi-slice splitting and signalanalysis to determine at which frequencies the change in impedance isthe greatest. This estimation helps in characterizing thebio-electrochemical reactions occurring on the surface of theelectrodes. The microcontroller 100 uses the change in amplitude andphase to calculate the concentration of the molecule in the sample.

The disclosed potentiostat may also vary the angular orientation of thesecond-third electrode's electric field with respect to the orientationof the first-second electrode's electric field. By default, if the thirdelectrode is disposed parallel to the first and second electrodes, theelectric field of the second-third electrodes is oriented perpendicularto the electric field of the first-second electrodes. On the other hand,if the third electrode is disposed perpendicular to the first and secondelectrodes, the electric field of the second-third electrodes isoriented parallel to the electric field of the first-second electrodes.During testing, the potentiostat varies the orientation of the electricfield of the second-third electrodes and measures the current responseat the third electrode. The electric field used in this process is givenby the following equation:{right arrow over (E)}=Em sin(ωt+Ø)×Ψ_(φ)where Em is the magnitude of the electric field, ω is the angularfrequency, t is time, Φ is phase, X represents the cross product of thevectors, and Ψ_(Φ) is the angular orientation of the electric field.Ψ_(Φ) is a unity constant for the first-second electrodes' electricfield. When the first, second, third electrodes are all planar, Ψ_(Φ) is90 degrees+θ for the third-second electric field, where θ is a variablethat rotates the electric field from 0 to 360 degrees. When the thirdelectrode is perpendicular to the first and second electrodes, Ψ_(Φ) is0 degrees+θ for the second-third electric field, where θ is a variablethat rotates the electric field from 0 to 360 degrees. While θ isvaried, the system measures the current response at the third electrode.The angular orientation of the electric field versus the currentresponse is unique for each target analyte, and is used by the system todetect the presence of target analytes.

Before being used to measure unknown quantities of a target analyte, thehandheld potentiostat must be calibrated. Calibration is performed bymeasuring the impedance of solutions containing known quantities of atarget analyte. Specifically, the user may perform impedancemeasurements of preferably four different solutions containing fourdifferent concentrations of the target analyte. For each calibrationtest, the user inputs the target analyte concentration into the handheldpotentiostat using the mini-joystick. The handheld potentiostat recordsthe impedance for each test. After the tests are completed, the systemcompletes the calibration by determining the coefficients in thefollowing equation,z _(i) =b _(n) x ^(n) +b _(n-1) x ^(n-1) + . . . +b ₁ x+cwhere z_(i) is the measured impedance, x is the known concentration ofthe target analyte, and b_(n), b_(n-1), b₁, and c are the coefficients.The order of the polynomial, n, may be between two and five, andpreferably two. The handheld potentiostat determines the unknown valuesof the coefficients using linear regression and least squares analysis.

In some embodiments, the microcontroller 100 is an Intel®microcontroller. In other embodiments, the microcontroller 100 is anIntel® microprocessor. In other embodiments, the microcontroller 100 isan ARM Cortex™-M microcontroller. In other embodiments, themicrocontroller 100 is an ARM Cortex™ microprocessor.

In particular embodiments, the microcontroller 100 applies an AC voltagebetween 5 mV and 500 mV to first electrode 108 and second electrode 106and to third electrode 110 and second electrode 106. The microcontrollerapplies an AC voltage whose frequency ranges between 50 Hz and 1,000 Hzto the electrodes. When a varying voltage is applied, a capacitivedouble layer is formed in the solution. As the frequency of the appliedvoltage increases, the distance of the capacitive layer from theelectrodes increases. In some embodiments, the user selects a minimumand a maximum frequency, and the microcontroller 100 applies voltageshaving frequencies ranging between the selected minimum and maximumfrequencies.

In some embodiments, the handheld potentiostats disclosed herein performimpedance spectroscopy analysis on a biosensing platform. Very lowvoltage is necessary for the use of these potentiostats in order to beapplicable for biosensing, as proteins and biomolecules are sensitive.In some embodiments, the range of appropriate voltage may be may be 50mV to 500 mV, but the appropriate voltage will depend on theapplication. In applications to protein based sensing, the voltages willbe in the range of 5 mV to 20 mV. In application to cells and DNA, thevoltage ranges will be between 100 mV to 2V. Similarly, due to theapplication of very small voltages, the current response is in a similarrange or much lower, as there is loss due to bulk solution medium. Insome embodiments, the range of appropriate current is 10 pA to 10 mAand, as with the voltage, the appropriate current response will dependon the application. In applications to protein based sensing, thecurrent response will be in the range of 10 pA to 100 nA. In applicationto cells and DNA, the current response will be between 100 nA to 10 mA.

The disclosed potentiostats may be used at fixed or variablefrequencies. Based on the application, the fixed and variable frequencyranges will vary. For most biosensing applications, the range offrequencies used is between 50 Hz and 100 kHz. Upon optimization of theelectrical debye length changes corresponding to a protein of interest,the fixed frequency can be estimated. Detection at the respectivefrequency can improve detection speeds and reduce non-specific signals.

In addition to performing impedance spectroscopy, the handheldpotentiostats disclosed herein can be used as a source meter and also asa voltammetry tool through easy-to-choose options on the LCD display.

The handheld potentiostats disclosed herein are easily portable and havea hand friendly form factor. It may be about or at least 1, 2, 3, 4, 5,6, 7, 8, 9, or 10 inches by about or at least 1, 2, 3, 4, 5, 6, 7, 8, 9,or 10 inches. It is specifically contemplated that it may be about 5inches by about 3 inches. It is also specifically contemplated that theentire device, including the programmable gain amplifier, theprogrammable microcontroller, and the LCD display for output that areindicated on the diagram, be within these sizes.

A diagram depicting a smartphone embodiment of the handheld potentiostatis found at FIG. 8. The handheld potentiostat comprises a smartphone 300and a potentiostat adaptor 306. The smartphone is operably coupled to apotentiostat adaptor 306 using a cable 304, preferably a Micro USB or aproprietary connector. The cable 304 provides bi-directionalcommunication between the smartphone 300 and the potentiostat adaptor306. The potentiostat adaptor comprises a first electrode port 202, asecond electrode port 204, a third electrode port 206, a microcontroller100, and a programmable gain amplifier 102. Users install a custompotentiostat software application onto the smartphone 300 that providesuser input and output and microcontroller communication functionality.Users may provide input to the smartphone 300, including the inputvoltage, input frequency, and wave type, using a touchscreen 302. Inother embodiments, users provide input to the smartphone using a keypad.The smartphone 300 displays output, such as the concentration of thetarget analyte on the smartphone's touchscreen 302.

The potentiostats disclosed herein also perform with low noise thresholdat the desired range of operation for biosensing. Currently,potentiostats are designed with electrochemical applications in mind.The integrated circuits used for these applications have reasonablenoise thresholds. When applying to biosensing, the measured signals ofthe available devices are in many cases within the noise threshold, thusrendering majority of the available potentiostats unsuitable.

The potentiostats disclosed herein are also programmable to performthree electrode impedance spectroscopy using fast Fourier transforms andLaplace transforms. Existing potentiostats use Lissajous curves methodsto estimate phase change in the measured current response. Though thishas been perfected for applications involving high voltages andcurrents, it is not optimized for analysis of voltage and currentresponses as necessary for biosensing. Fast Fourier transform-based andLaplace transfer-based estimation, which is more appropriate for theseapplications, has not been widely used due to complexity inimplementation as it demands high processor speeds. Using fast Fourierand Laplace transforms assists in digital signal analysis by reducingnoise and preserving signal integrity; both of which are critical forbiosensing.

The potentiostat's calculations using fast Fourier transforms isdescribed below. The microcontroller applies a sinusoidal voltage of theform V(t)=v sin(ωt), where v is the amplitude of the signal and ω is theangular frequency. In preferred embodiments, the microcontroller appliessinusoidal voltages at varying frequencies. The microcontroller measuresthe resulting current signal, which is of the form I(t)=i sin(ωt+φ),where i is the amplitude of the signal and φ is the phase shift of thesignal. The microcontroller converts the applied voltage signal from thetime domain into the frequency domain by applying a fast Fouriertransform,

${V(\omega)} = {{\sum\limits_{n = 0}^{{N/2} - 1}{{v(t)}_{n}^{even}e^{{- 2}\;\pi\; j\;{{nk}/{(\frac{N}{2})}}}}} + {e^{{- 2}\;\pi\; j\;{k/N}}{\sum\limits_{n = 0}^{\frac{N}{2} - 1}{{v(t)}_{n}^{odd}{e^{{- 2}\;\pi\; j\;{{nk}/{(\frac{N}{2})}}}.}}}}}$Likewise, the microcontroller converts the resulting current signal fromthe time domain into the frequency domain in step 506 by applying a fastFourier transform,

${I(\omega)} = {{\sum\limits_{n = 0}^{{N/2} - 1}{{i(t)}_{n}^{even}e^{{- 2}\;\pi\; j\;{{nk}/{(\frac{N}{2})}}}}} + {e^{{- 2}\;\pi\; j\;{k/N}}{\sum\limits_{n = 0}^{\frac{N}{2} - 1}{{i(t)}_{n}^{odd}{e^{{- 2}\;\pi\; j\;{{nk}/{(\frac{N}{2})}}}.}}}}}$The resulting current frequency signal is verified with the appliedvoltage signal and noise occurring at other frequencies is filtered out.The microcontroller determines the frequency at which the maximumimpedance change occurred using multi-slice splitting, wherein theapplied frequency spectrum is sliced into individual discrete frequencypoints. The microcontroller then compares the frequency at which themaximum impedance change occurred to the reference frequency pointstored in memory for the specific analyte being tested. Themicrocontroller estimates the concentration of the tested analyte byapplying the same equation used in calibration,z_(i)=b_(n)x^(n)+b_(n-1)x^(n-1)++b₁x+c, where z_(i) is the impedance atthe frequency at which the maximum impedance change occurred, and b_(n),b₁, and c are coefficients calculated during calibration, and x is thetarget analyte concentration being computed. In preferred embodiments,the equation is quadratic.

FIG. 12 is a flowchart illustrating the operation of one embodiment ofthe potentiostat. At step 800, a sinusoidal voltage is applied betweenthe first and second electrodes. At step 802, the system measures theresulting current flowing between the first and second electrodes. Atsteps 804 and 806, the voltage and current are converted into frequencydomain signals using a fast Fourier transform. In step 808, the voltageand current are converted into s domain signals using a Laplacetransform. In step 810, the sinusoidal voltage applied to the first andsecond electrodes is applied at different frequencies, which results inthe capacitive double layer being formed at different distances from theelectrodes. In step 812, the modulus and imaginary part of the impedanceare analyzed with the change in applied signal frequency. At step 814,distinctive markers in the solution are identified based upon themeasured reactance at different frequencies. At step 816, the systemapplies a sinusoidal voltage between the third and second electrodes. Atstep 818, the system measures the resulting current flowing between thethird and second electrodes. At steps 820 and 822, the system applies afast Fourier transform to convert the applied voltage and resultingcurrent signals into the frequency domain. In step 824, the signals areconverted into the s domain using a Laplace transform. In step 826, theresultant electric field is applied at varying angles which areorthogonal to the first-second electrode. At step 828, the rotationalangle and current response is analyzed. At step 830, the systemdetermines the presence of one or more analytes in solution based uponthe current response exhibited at different angular electric fields.

The potentiostats disclosed herein also contain cost-effectivecomponents, manufacturing involves very simple surface mount deviceassembly, and the disclosed devices have low-thermal noise due to use ofmodern current amplifiers and programmable gate arrays.

Finally, the potentiostats disclosed herein have applicability as asource meter, a voltammetry tool, and for standard current measurements.The potentiostats can be customized for the different applications bymaking modifications to the program that run the operations and produceresults. The programmable gain amplifiers have a broad range ofoperation (mV-V/pA-mA) and hence can be used for different voltammetryapplications to biosensing as well as general applications.Microprocessors/microcontrollers offer extensive programming libertiesand hence application of the potentiostats to different operations willrequire only software changes and not hardware.

The potentiostats disclosed herein are highly adaptable and generatesresults rapidly. For a single channel assay, when a single channel EIMdetection scheme and a 32-bit microcontroller (40-10 kHz) is used, itresults in a read time of less than 40 seconds.

B. Substrates and Conductive Materials

The substrates contemplated include porous nanotextured substrates. Insome embodiments, paper, nitrocellulose, fabric, leaves, bark, or shellsis contemplated; however, any porous, hydrophilic substrate that wicksfluids by capillary action can be used as the substrate in the methodsand devices described herein. Non-limiting examples include celluloseand cellulose acetate, paper (e.g., filter paper and chromatographypaper), cloth or fabric, porous polymer film, porous plastic, or leaves.In some embodiments, the substrate is biodegradable. Preferably, thesubstrate is paper.

The porosity of the substrate in conjunction with conductive ink screenprinting can be leveraged to pattern conformal circuits. Any size andthickness of substrate may be used. The dimensions of the substrate arenot key to functionality of the circuit. The critical parameter thatimpacts the performance of the circuit is the porosity of the substrate.Porosity can vary from 10×10⁷ to 10×10¹⁸ pores/mm² and the substrate,including its porosity, is selected based on the size of the targetanalyte. This porosity can be adjusted or tuned using a variety oftechniques, e.g., coatings or treatments. Examples of possibletreatments and coatings include wet treatments such as acidic oralkaline etching, use of layer by layer deposition of self-assembledmonolayers, and dry treatments such as reactive ion etching and plasmaetching.

The substrate can be up to 100 microns thick, and there are no cappingfactors on the lateral dimensions. In some embodiments, the substratemay be 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 cm by 1, 2, 3, 4, 5, 6, 7, 8, 9,or 10 cm, or any size in between. In particular embodiments, thesubstrate is 1 cm by 1 cm.

It is contemplated that any appropriate conductive material may be used,and a range of conductive inks are contemplated. Conductive inks usuallycontain conductive materials such as powdered or flaked silver andcarbon like materials. In some embodiments, the conductive ink iscarbon, silver, or metal or metal oxide nanoparticle-infused carboninks. In some embodiments, the metal or metal-oxide nanoparticle-infusedcarbon ink is 1% by volume infused with a noble metal or metal oxide. Incertain examples, the carbon ink is infused with gold, platinum,tantalum, silver, copper, tin, indium-tin oxide, grapheme, graphemeoxide, zinc oxide, titanium oxide, iron oxide, or molybdenum oxide. Theuse of additives such as metal or metal oxide nanoparticles to carbonink changes the conductive carbon ink into semi-conducting ink. In someembodiments, this semi-conducting ink pattern may be used for designingthe diode and transistor behavior. In some embodiments, nativeconducting ink may be used for obtaining the impedance changes. The inksubstrate (i.e., the combination of the ink and the substrate) is thebase electrode surface over which the biomolecule chemistry isimplemented for achieving molecular diagnostics.

The nature of the ink is dependent on the type of sensing and analysisdesired. In some embodiments, when passive sensing with an electricalreader is necessary, the ink is only conducting. More particularly, forpassive devices, conductive/semi-conducting nanoparticles may bedispersed in a matrix, or the ink may contain metal nanoparticles, metaloxide nanoparticles, or electro active polymer matrices. In situationswhere active sensing, such as with a multimeter, is useful, the ink canbe conducting and semi-conducting, or conducting stacks. Where opticalsensing is appropriate, the ink may be photo catalytic. In situationswhere colorimetric sensing is useful, the ink will contain nanoparticlesthat agglomerate during sensing. Hybrid stacking of material can alsogive additional properties to the ink.

In some embodiments, the conformal circuit may include a redox material,such as derivatives of copper, potassium, magnesium, and rubidium. Thesematerials bind with the receptor of the analyte immobilized onto theconformal circuit. During the binding of the analyte onto the receptorwith the redox material there is an amplification in the number ofcharges routed through the conformal circuit due to the reduction oroxidation of the redox material. This process is distinct from the useof redox electrodes, where the redox material is immobilized onto theredox electrode itself. During the application of a bias potential or acurrent to the redox material on a redox electrode, this material eitherundergoes a reduction or oxidation, thus binding to the target analytein this state and modifying the analyte that is being tested/evaluated.

C. Methods of Patterning

The conformal circuits are assembled by performing engineering tostandard paper products. Porosity in paper is leveraged towardsachieving control in circuit formation. A stencil of the circuit designis transferred onto the substrate surface in any appropriate manner. Theparameters of the desired pattern are determined by the molecules to bedetected. A person of skill in the art would recognize the appropriatetransferring method in view of the desired pattern. For example, smallerpatterns or smaller feature sizes require the more advanced printingtechniques, e.g., masking and lithography. These processes are discussedin more detail below.

Stencils contain a pattern of holes or apertures through whichconductive materials could be deposited onto the hydrophilic substrates.Alternatively, in an etching process, stencils contain a pattern ofholes or apertures through which conductive materials could be etched toform a pattern of metal on the hydrophilic substrates. Stencils could bemade from a variety of materials such as metal, plastic, or patternedlayers of dry-film resist. Non-limiting examples of metals formanufacturing stencils include stainless steel and aluminum.Non-limiting examples of plastic for manufacturing stencils includemylar. Alternatively, patterned layers of dry-film resist can be used asstencils. In one or more embodiment, metals or plastics are used tomanufacture stencils and patterns of metallic pathways can be designedon a computer using a layout editor, (e.g., Clewin, WieWeb Inc.) andstencils based on the design can be obtained from any supplier (e.g.,Stencils Unlimited LLC (Lake Oswego, Oreg.)). In certain embodiments,the stencil can be removed from the paper after deposition. In certainother embodiments, one side of the stencil is sprayed with a layer ofspray-adhesive (e.g., 3M Photomount, 3M Inc.) to temporarily affix thestencil to the paper substrate. After deposition, the stencil can bepeeled away from the paper. The stencils can be reused multiple times,e.g., more than 10 times. In other embodiments, patterned layers ofdry-film resist can be used as stencils. Dry film resist can bepatterned when exposed to UV light through a transparency mask anddeveloped in dilute sodium hydroxide solution. The patterned dry-filmresist can be attached to a coating sheet of plastic or directly affixedto the hydrophilic substrates by pressing the resist-side to the surfaceof the hydrophilic substrates and passing multi-sheet structure throughheated rollers in a portable laminator (Micro-Mark, Inc.). The coatingsheet of plastic can then be peeled away, resulting in a sheet of paperwith dry film resist patterned on one side.

A variety of deposition methods could be used to deposit electricallyconductive materials onto the hydrophilic substrates of the microfluidicdevices. Non-limiting examples of the deposition methods includedepositing conductive materials using stencils, depositing conductivematerials by drawing conductive pathways, depositing conductivematerials by inkjet or laser printing, depositing conductive materialsby attaching commercially available or homemade conductive materialtapes onto the hydrophilic substrates, depositing conductive materialsby drawing conductive pathways, or depositing conductive materials byintroducing conductive fluids onto the hydrophilic substrates or thehydrophilic channels of the microfluidic devices. Alternatively,conductive materials could be embedded in the pulp or fibers formanufacturing the hydrophilic substrates to allow for manufacturinghydrophilic substrates containing conductive materials.

It is specifically contemplated that the circuit design may betransferred onto the substrate surface either through (a) dip coating(b) embossing or (c) masking and lithography. Dip coating and embossingallow for feature resolution in hundreds of microns, more particularlyup to 100 nanometers/0.1 micron, and masking and lithography allows forfeature resolution in 1-10 micron regime. These techniques are wellknown to those of skill in the art. See Reighard and Barendt, 2000. Inparticular embodiments, the circuit may be designed on a 3D printer andthe design may be transferred to the substrate by embossing the circuitonto the substrate.

The lateral porosity of the substrate is leveraged to generate theconformal circuits disclosed herein. Vertical porosity is not suitable,and therefore a metal barrier of thickness in the order of 100 s of nmachieves this goal. The thickness of deposited material also correspondsto the thickness of the substrate in some regions to change theelectrical behavior of the substrate.

In a particular embodiment, the entire paper surface is dip coated.Biomolecules interacting with the conductive ink surfaces alone areresponsible for the measured signal. There are no flow considerations tobe taken into account. Hence, biomolecule interactions are primarilydiffusion and capillary action driven and therefore larger the poresfaster is the interaction. Multiple layers of dip coating have beenadopted, where appropriate. This technique is most relevant when theintent is to design immunoassays requiring multiple layers of moleculesincorporated onto the sensor platform.

D. Detection of Biomolecules

These conformal circuits can be applied for a wide range of moleculardiagnostics and analysis, and therefore can be used on any sample thatis suspected of containing a molecule of interest such as food, water,soil, air, bodily fluids such as blood serum, detergents, ionic buffer,etc. In some embodiments, the sample is any liquid sample or solid thatcan be solubilized or dispersed in a liquid. In other embodiments, thecircuits can be used to detect toxins or other molecules in an airsample. For example, the circuit can be used to detect carbon monoxide,greenhouse gases such as NO_(x), SO_(x), NH₄, O₃, and otherenvironmental toxins. The circuits can be used to design simple affinitybased assays for mapping presence of enzymes and physiological ions.These can be used to develop assays to study antibody-antigeninteractions and to determine presence or absence of a wide range ofprotein biomarkers expressed at ultra-sensitive concentrations. Genomicassays can also be developed using these circuits.

A single step immunoassay can be used in connection with the conformalcircuits. In some embodiments, label free immunoassays usingelectrochemical sensors are appropriate (Vertergaard, et al., 2007). Ina particular embodiment of protein diagnostics, a single primaryantibody without a tag is used and, based on the base circuit,controlled and mapped modulations to the electrical circuit parametersare achieved during detection of the proteins. The system can bedesigned to detect quantitatively (e.g., an electrochemical impedancespectroscopy electronic reader).

The conformal circuits disclosed herein may be prepared for theimmunoassay in any appropriate manner. In one embodiment, a linker isdeposited on the substrate, the substrate is saturated with a moietyspecific for the target analyte, e.g., a target specific antibody, ablocking buffer is applied to the receptor moiety saturated conformalcircuit surface to minimize nonspecific binding or adsorption of othercompeting molecules onto the sensor surface, a buffer wash is performed,and the target analyte, e.g., antigen, is dosed onto the circuit. Indesigning the calibration curve for a target molecule, such as anantigen, increasing doses of the antigen are applied onto the conformalcircuit and impedance measurements are obtained until steady state isreached. An increasing change to the measured impedance is expected withincreasing dose of the target molecule such as an antigen. Once thecalibration curve has been designed, an unknown dose of a test targetmolecule such as an antigen is tested onto the antibody/receptor moietysaturated sensor surface, and the change in impedance is then evaluatedagainst the calibration curve to determine the dose of the test targetmolecule.

Analyte confinement is achieved within the nanoscale texture of thesubstrate, and the size-based confinement of the target analyte onto thesubstrate is achieved using conductive ink. Analytes interacting withthe conductive ink in a single step immunoassay format perturb the (a)electrical double layer, (b) charges in the depletion layer in thediode, and (c) gate current characteristics of transistor resulting inthe detection of the biomolecule of interest. As ultra-low volumes inthe range of 1-10 micro liters are needed, the issue of controlled flowdoes not exist. Primarily spotting of the fluid on the substrate surfaceis sufficient to achieve associated interaction for biomoleculedetection.

The conformal circuit and detection devices disclosed herein can bedesigned to detect either quantitatively (e.g., an EIS electronicreader) or qualitatively (e.g., color change). In addition, the systemcan be designed to detect a singlet (one analyte), multiplex (multipleanalytes of same type), or multiplexicity (multiple analytes ofdifferent types).

The conformal circuits disclosed herein are highly versatile. For asingle channel assay, a sample volume of less than 125 μL is needed, ithas a dynamic range of detection of 1 pg/mL-10 μg/mL, and it can beuseful for molecules at or between 1 and 100 nm. For multi-channeldetection, a sample volume of less than 75 μL is needed, it has adynamic range of detection of 1 pg/mL-10 μg/mL, there can be a minimumof 2 channels and a maximum of 8 channels, and it can be useful formolecules at or between 1 and 100 nm. For multiplexicity detection, asample volume of less than 50 μL is needed, it has a dynamic range ofdetection of 1 pg/mL-10 μg/mL, there can be a minimum of 2 channels anda maximum of 16 channels, and it can be useful for molecules at orbetween 1 and 100 nm.

The potentiostats disclosed herein are highly adaptable and generatesresults rapidly. For a single channel assay, when a single channel EIMdetection scheme and a 32-bit microcontroller (40-10 kHz) is used, itresults in a read time of less than 40 seconds. For multi-channeldetection, when a serial multi-channel EIM and a 16-bit/32-bitmicrocontroller (40-10 kHz) is used with a minimum of 2 channels and amaximum of 8 channels, results are generated in less than 40 seconds perchannel. For multiplexicity detection, when a parallel multi-channel EIMand a 32-bit/64-bit microcontroller (40-10 kHz) is used with a minimumof 2 channels and a maximum of 16 channels, results are generated inless than 30 seconds per channel.

E. Kits

In some embodiments, contemplated are kits comprising conformal circuitsand a potentiostat. In some embodiments, these kits are designed toaccommodate a particular target analyte, e.g., a particular protein ofinterest. In one embodiment, the kit will comprise conformal circuitscomprising a nanotextured porous substrate which is appropriate for thetarget analyte, which will have an appropriate pattern transferred toit, where the pattern is made up of an appropriate ink. In addition, thekit will further comprise a potentiostat which is calibrated to generatethe data of interest to the user for the particular target analyte.

For example, a conformal circuit designed to detect C-reactive proteinwould have a substrate of nanoporous material, e.g., paper, having aporosity of 10¹³ to 10¹⁵ pores/cm² of 200 nm pores, where the circuit ismade of a pattern that is interdigitated or edge-free interdigitated, ora concentric ring made using metal or metal-oxide nanoparticle-infusedcarbon ink infused with gold/platinum/silver/copper/nickel/indium tinoxide/iron oxide. The parameters of interest that would be inputted intothe potentiostat include the applied voltage of 10 mV and an appliedfrequency and range of 20 to 10 KHz. Finally, the parameters of interestfor analysis include the frequency of analysis, applied voltage, currentmeasured, calculated impedance, estimated concentration, and standardcalibration curve.

F. Examples

The following examples are included to demonstrate preferred embodimentsof the invention. It should be appreciated by those of skill in the artthat the techniques disclosed in the examples which follow representtechniques discovered by the inventor to function well in the practiceof the invention, and thus can be considered to constitute preferredmodes for its practice. However, those of skill in the art should, inlight of the present disclosure, appreciate that many changes can bemade in the specific embodiments which are disclosed and still obtain alike or similar result without departing from the spirit and scope ofthe invention.

FIG. 9 is a Bode plot representing the impedance modulus versusfrequency of the applied signal for a solution containinglipopolysaccharide, lipoteichoic acid, and Troponin-T. FIG. 9illustrates the frequency at which capacitance and resistance dominanceis observed. The plot demonstrates the presence of distinct proteinbiomarkers in the solution, but does not quantify the protein biomarkersor their specificity in binding.

FIG. 10 is another Bode plot representing phase change in the impedanceversus the frequency of the applied signal for a solution containinglipopolysaccharide, lipoteichoic acid, and Troponin-T. The proteinbiomarkers exhibit unique impedance phase profiles that demonstrate theability to distinguish multiple biomarkers in solution based uponspectroscopic analysis. The plot does not quantify the proteinbiomarkers or their specificity in binding.

FIG. 11 is a plot of the angular orientation of the second-thirdelectrode electric field versus the measured output current at the thirdelectrode for a solution containing lipopolysaccharide, lipoteichoicacid, and Troponin-T. The protein biomarkers detected at theelectrode-solution interface demonstrate unique phase responseproperties under the influence of orthogonally intersecting electricfields. The three protein biomarkers tested demonstrate unique currentresponses at varied orientation angles of applied electric fields.

FIG. 13 is a table listing various species of target analytes system andassociated system configurations.

G. Experimental Data

FIG. 14 is a graph of a change in impedance (measured in ohms) versusconcentration of lipopolysaccharide (measured in fg/mL) as detected byan exemplary embodiment of the present disclosure.

FIG. 15 is a graph of a change in impedance (measured in ohms) versusconcentration of procalcitonin (measured in fg/mL) as detected by anexemplary embodiment of the present disclosure.

FIG. 16 is a graph of a change in impedance (measured in ohms) versusconcentration of lipoteichoic acid as (measured in fg/mL) detected by anexemplary embodiment of the present disclosure. The linear range ofoperation for the detection of lipopolysaccharide, procalcitonin, andlipoteichoic acid was 1 fg/mL-1 μg/mL.

Additional data was collected regarding the detection of miRNA 21. Thedetection of small RNA molecules to study regulation of target geneexpression has shown value. For example, miRNA's are key players incancer regulation. In one test, the number of copies of miRNA 21 in acell lysate solution was detected. The test sample included miRNA 21enriched cells. A 20 bp oligo nucleotide on a paper cartridge targetedmiRNA 21, and the control was wilde-type cells. A high relativeconcentration of miRNA 21 (e.g. greater than 200 copies/cell) wasdetected.

Additional data was collected regarding the detection of miRNA sequence(P4) with a specific capture probe (P2). FIG. 17 represents the measuredimpedance (in ohms) at various temperatures and times. The impedance atthe capture probe was 32.452 kohms.

An estimation of signal for interaction of non-specific miRNA sequencewith capture probe (P2) is shown in FIG. 18.

FIG. 19 illustrates an estimation of signal for interaction of salmonsperm DNA with capture probe (P2).

REFERENCES

The following references, to the extent that they provide exemplaryprocedural or other details supplementary to those set forth herein, arespecifically incorporated herein by reference.

-   Reighard & Barendt, “Conformal Coating Process Controls: The    Manufacturing Engineer's Aid.” APEX. Long Beach, Calif. March 2000.-   Vestergaard, et al., Sensors. 7(12):3442-58, 2007.

What is claimed is:
 1. A method of detecting or quantifying multipletypes of target analytes in a sample using a handheld measuring deviceand a conformal analyte sensor circuit comprising the steps of: (a)placing a sample containing multiple target analytes on a conformalsubstrate having a sensor circuit comprising a first electrode, a secondelectrode, and a third electrode, wherein the sensor circuit of theconformal analyte comprises: a solid substrate having a top surface,wherein the solid substrate comprises a porous nanotextured substratethat is an insulating substrate; and a conductive material stenciled onthe top surface of the solid substrate in a circuit design; (b) applyinga first electric field with a first alternating electric voltage betweenthe first electrode and the second electrode at a first phase angle; (c)applying a second electric field with a second alternating electricvoltage between the third electrode and the second electrode at a secondphase angle, wherein the first electric field and the second electricfield are locked in phase and wherein the first phase angle and thesecond phase angle are separated by a constant delta phase angle; (d)measuring the output current at different frequencies and varying phaseangles for different analytes; (e) amplifying an output current flowingfrom the first electrode and from the third electrode through the secondelectrode using a programmable gain amplifier; (f) varying the firstphase angle of the first alternating electric voltage and the secondphase angle of the second alternating electric voltage; (g) identifyingthe first phase angle and the second phase angle at which a maximumimpedance change occurs; (h) measuring the impedance identified at thefirst phase angle and the second phase angle, wherein the measuredimpedance is non-faradaic; and (i) using the measured impedance andassociated phase angle and output current at different frequencies todetect multiple target analytes or calculate concentrations of targetanalytes by use of a standard calibration curve.
 2. A method ofdetecting or quantifying a target analyte in a sample using a handheldmeasuring device and a conformal analyte sensor circuit comprising thesteps of: (a) placing a sample containing multiple target analytes on aconformal substrate having a sensor circuit comprising a firstelectrode, a second electrode, a third electrode, a fourth electrode, afifth electrode and a sixth electrode, wherein the sensor circuit of theconformal analyte comprises: a solid substrate having a top surface,wherein the solid substrate comprises a porous nanotextured substratethat is an insulating substrate; and a conductive material stenciled onthe top surface of the solid substrate in a circuit design; (b) applyinga first electric field with a first alternating electric voltage betweenthe first electrode and the second electrode at a first phase angle; (c)applying a second electric field with a second alternating electricvoltage between the third electrode and the second electrode at a secondphase angle, wherein the first electric field and the second electricfield are locked in phase and wherein the first phase angle and thesecond phase angle are separated by a first constant delta phase angle;(d) measuring a first output current at different frequencies over afirst range of frequencies and varying phase angles over a first rangeof phase angles; (e) amplifying the first output current flowing fromthe first electrode and from the third electrode through the secondelectrode using a programmable gain amplifier; (f) varying the firstphase angle of the first alternating electric voltage and the secondphase angle of the second alternating electric voltage over the firstrange of phase angles; (g) identifying the first phase angle and thesecond phase angle at which a first maximum impedance change occurs; (h)measuring the impedance identified at the first phase angle and thesecond phase angle, wherein the measured impedance is non-faradaic; (i)using the measured impedance at different frequencies to detect a firsttarget analyte or calculate a concentration of the first target analyteby use of a standard calibration curve; (j) applying a third alternatingelectric voltage between the fourth electrode and the fifth electrode ata third phase angle; (k) applying a fourth alternating electric voltagebetween the sixth electrode and the fifth electrode at a fourth phaseangle, wherein the third phase angle and the fourth phase angle areseparated by a second constant delta phase angle; (l) measuring a secondoutput current at different frequencies over a second range offrequencies and varying phase angles over a second range of phaseangles; (m) amplifying the second output current flowing from the fourthelectrode and from the sixth electrode through the fifth electrode usingthe programmable gain amplifier; (n) varying the third phase angle ofthe third alternating electric voltage and the fourth phase angle of thefourth alternating electric voltage over the second range of phaseangles; (o) identifying the third phase angle and the fourth phase angleat which a second maximum impedance change occurs; (p) measuring theimpedance identified at the third phase angle and the fourth phaseangle; and (q) using the measured impedance and phase change atdifferent frequencies to detect a second target analyte or calculate aconcentration of the second target analyte by use of a standardcalibration curve.
 3. The method of claim 2 wherein the first range offrequencies and the second range of frequencies are different.
 4. Themethod of claim 2 wherein the first range of phase angles and the secondrange of phase angles are different.
 5. The method of claim 2 whereinthe first range of frequencies and the second range of frequencies areequal.
 6. The method of claim 2 wherein the first range of phase anglesand the second range of phase angles are equal.
 7. The method of claim 2wherein steps (a)-(i) are performed concurrently with steps (j)-(q). 8.A method of detecting or quantifying a target analyte in a sample usinga handheld measuring device and a conformal analyte sensor circuitcomprising the steps of: (a) applying a first input electric voltagebetween a first electrode and a second electrode of a conformal analytesensor circuit, wherein the conformal analyte sensor circuit comprises:a solid substrate having a top surface, wherein the solid substratecomprises a porous nanotextured substrate that is an insulatingsubstrate; and a conductive material situated on the top surface of thesolid substrate in a circuit design, thereby creating a circuitcomprising the first electrode, the second electrode, and a thirdelectrode, wherein the conductive material is a conductive ink orsemi-conductive ink; (b) applying a second input electric voltagebetween the third electrode and the second electrode of the conformalanalyte sensor circuit; (c) amplifying an output current flowing fromthe first electrode and from the third electrode through the secondelectrode using a programmable gain amplifier; (d) calculating animpedance by comparing the first input electric voltage and the secondinput electric voltage to the output current using a programmablemicrocontroller, wherein the calculated impedance is non-faradaic; and(e) detecting a target analyte or calculating a target analyteconcentration from the calculated impedance using a programmablemicrocontroller.
 9. A method of detecting or quantifying multiple targetanalytes in a sample using a handheld measuring device and a conformalanalyte sensor circuit comprising the steps of: (a) applying a firstinput electric voltage between a first electrode and a second electrodeof a conformal analyte sensor circuit, wherein the conformal analytesensor circuit comprises: a solid substrate having a top surface,wherein the solid substrate comprises a porous nanotextured substratethat is an insulating substrate; and a conductive material situated onthe top surface of the solid substrate in a circuit design, therebycreating a circuit comprising the first electrode, the second electrode,and a third electrode, wherein the conductive material is a conductiveink or semi-conductive ink; (b) applying a second input electric voltagebetween the third electrode and the second electrode of the conformalanalyte sensor circuit; (c) shifting an angular orientation of anelectric field of the second input electric voltage; (d) amplifying anoutput current flowing through the first electrode using a programmablegain amplifier; (e) calculating an impedance by comparing the firstinput electric voltage and the second input electric voltage to theoutput current using a programmable microcontroller, wherein thecalculated impedance is non-faradaic; and (f) detecting a presence ofone or more target analytes by comparing the angular orientation of theelectric field to the output current.
 10. The method of claim 1, whereinthe first alternating electric voltage and the second alternatingelectric voltage have a frequency between 50 Hz and 5,000 Hz.
 11. Themethod of claim 1, wherein the first alternating electric voltage andthe second alternating electric voltage are between 100 mV and 500 mV.